Cartridge for conducting a chemical reaction

ABSTRACT

A device for conducting a chemical reaction comprises a body having at least first and second channels formed therein. A reaction vessel extends from the body. The reaction vessel has a reaction chamber, an inlet port connected to the reaction chamber via an inlet channel, and an outlet port connected to the reaction chamber via an outlet channel. The inlet port of the vessel is connected to the first channel in the body, and the outlet port of the vessel is connected to the second channel in the body.

RELATED APPLICATION INFORMATION

This application claims priority from provisional application No.60/136,703 filed May 28, 1999 which is incorporated by reference hereinfor all purposes.

FIELD OF THE INVENTION

The present invention relates generally to the field of biochemicalanalysis, and in particular to a novel cartridge for conducting achemical reaction.

BACKGROUND OF THE INVENTION

The analysis of clinical or environmental fluids generally involves aseries of chemical, optical, electrical, mechanical, or thermalprocessing steps on the fluid samples. In recent years, there has beengrowing interest in developing disposable cartridges for conductinganalyses of biological samples for various diagnostic and monitoringpurposes. For example, U.S. Pat. No. 5,587,128 to Wilding disclosesdevices for amplifying a preselected polynucleotide in a sample byconducting a polynucleotide amplification reaction. U.S. Pat. No.5,922,591 to Anderson et al. describes a miniaturized, integratednucleic acid diagnostic device and system. The device is generallycapable of performing one or more sample acquisition and preparationoperations, in combination with one or more sample analysis operations.

Despite these advances, however, there remains a need for a cartridgethat permits the rapid thermal processing of a reaction mixture as wellas increased sensitivity in the detection of analyte in the mixture.

SUMMARY

The present invention provides an apparatus and method for analyzing afluid sample to determine the presence or absence of an analyte in thesample. The apparatus includes a cartridge for separating a desiredanalyte from the sample and for holding the analyte for a chemicalreaction and optical detection. The apparatus also includes aninstrument for receiving the cartridge for sample processing. Thedesired analyte may comprise, e.g., organisms, cells, proteins, nucleicacid, carbohydrates, virus particles, bacteria, chemicals, orbiochemicals. In a preferred use, the desired analyte comprises nucleicacid and the chemical reaction performed is nucleic acid amplificationusing, e.g., the polymerase chain reaction (PCR).

In accordance with an aspect of the present invention, a device forconducting a chemical reaction comprises a body having at least firstand second channels formed therein. A reaction vessel extends from thebody, the reaction vessel having a reaction chamber, an inlet portconnected to the reaction chamber via an inlet channel, and an outletport connected to the reaction chamber via an outlet channel. The inletport of the vessel is connected to the first channel in the body, theoutlet port of the vessel is connected to the second channel in thebody, and the body further includes a vent in fluid communication withthe second channel for venting gas from the second channel.

In accordance with another aspect of the present invention, a device forconducting a chemical reaction comprises a body having at least firstand second channels formed therein. A reaction vessel extends from thebody, the reaction vessel having a rigid frame defining side walls of areaction chamber, first and second polymeric films attached to oppositesides of the rigid frame to form opposing major walls of the reactionchamber, an inlet port connected to the reaction chamber via an inletchannel, and an outlet port connected to the reaction chamber via anoutlet channel. The inlet port of the vessel is connected to the firstchannel in the body, and the outlet port of the vessel is connected tothe second channel in the body.

In accordance with another aspect of the present invention, a device forconducting a chemical reaction comprises a body having a sample flowpath and having a separation region in the sample flow path forseparating a desired analyte from a fluid sample. A reaction vesselextends from the body, the reaction vessel having a reaction chamber, aninlet port connected to the reaction chamber via an inlet channel, andan outlet port connected to the reaction chamber via an outlet channel.The body further has at least first and second channels formed therein,the separation region being connected to the inlet port of the vesselvia the first channel in the body, and the outlet port of the vesselbeing connected to the second channel in the body.

In accordance with another aspect of the present invention, a device forconducting a chemical reaction comprises a body having at least firstand second channels formed therein. A reaction vessel extends from thebody, the reaction vessel having a plurality of walls defining areaction chamber. At least one of the walls comprising a flexible sheetor film. The vessel also has an inlet port connected to the reactionchamber via an inlet channel and an outlet port connected to thereaction chamber via an outlet channel. The inlet port of the vessel isconnected to the first channel in the body, and the outlet port of thevessel is connected to the second channel in the body. The device alsocomprises at least one thermal surface for contacting the sheet or film,means for increasing the pressure in the reaction chamber, wherein thepressure increase in the chamber is sufficient to force the sheet orfilm to conform to the thermal surface, and at least one thermal elementfor heating or cooling the surface to induce a temperature change in thechamber.

In accordance with another aspect of the present invention, a device forconducting a chemical reaction comprises a body having at least firstand second channels formed therein. A reaction vessel extends from thebody, the reaction vessel having a reaction chamber defined by twoopposing major walls and side walls connecting the major walls to eachother. At least two of the walls defining the reaction chamber areoptically transmissive. The reaction vessel also has an inlet portconnected to the reaction chamber via an inlet channel and an outletport connected to the reaction chamber via an outlet channel. The inletport of the vessel is connected to the first channel in the body, andthe outlet port of the vessel is connected to the second channel in thebody. The device also comprises optics for optically interrogating thereaction chamber, the optics comprising at least one light source fortransmitting light to the reaction chamber through a first one of theoptically transmissive walls and at least one detector for detectinglight exiting the chamber through a second one of the opticallytransmissive walls.

Another aspect of the invention is a method for conducting a chemicalreaction, the method comprising the step of introducing a sample into adevice comprising, a body having a sample flow path and having aseparation region in the sample flow path for separating a desiredanalyte from the sample. The device also comprises a reaction vesselextending from the body, the reaction vessel having a reaction chamber,an inlet port connected to the reaction chamber via an inlet channel,and an outlet port connected to the reaction chamber via an outletchannel. The body further has a first channel connected to the inletport of the vessel and a second channel connected to the outlet port ofthe vessel. The method also comprises the steps of separating theanalyte from the sample in the separation region, forcing the analyte toflow into the reaction chamber of the vessel via the first channel inthe body while air displaced from the reaction chamber exits through theoutlet channel and outlet port of the vessel into the second channel inthe body, and conducting a chemical reaction in the reaction chamber.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an isometric view of a cartridge for analyzing a fluid sampleaccording to a first embodiment of the invention.

FIG. 2 is a lower isometric view of the cartridge of FIG. 1.

FIG. 3 is an exploded view of the cartridge of FIG. 1.

FIG. 4 is another exploded view of the cartridge of FIG. 1.

FIG. 5 is a partially cut away view of an ultrasonic horn coupled to awall of a lysing chamber formed in the cartridge of FIG. 1.

FIG. 6 is an exploded view of a filter stack positioned in the lysingchamber of the cartridge of FIG. 1.

FIG. 7 is a top plan view of the cartridge of FIG. 1.

FIG. 8 is a bottom plan view of the cartridge of FIG. 1.

FIG. 9 is a schematic block diagram of the cartridge of FIG. 1.

FIG. 10 is an isometric view of an instrument into which the cartridgeof FIG. 1 is placed for processing.

FIG. 11 is an isometric view of the cartridge of FIG. 1 in theinstrument of FIG. 10.

FIG. 12 is a partially cut-away view of the cartridge of FIG. 1 in theinstrument of FIG. 10.

FIG. 13 is a schematic, plan view of optical sensors positioned todetect liquid levels in the cartridge of FIG. 1.

FIG. 14 is a partially cut away, schematic, side view of a slottedoptical sensor positioned to detect the liquid level in a sensor chamberof the cartridge of FIG. 1.

FIG. 15A is a cross-sectional view of a portion of the body of thecartridge of FIG. 1 illustrating two different types of valves in thecartridge.

FIG. 15B is a cross-sectional view of the valves of FIG. 15A in a closedposition.

FIG. 16A is another cross-sectional view of one of the valves of FIG.15A in an open position.

FIG. 16B is a cross-sectional view of the valve of FIG.

FIG. 16A in a closed position.

FIGS. 17-19 illustrate a valve actuation system for opening and closingthe valves of FIG. 15A.

FIG. 20 is a cross sectional view of alternative valve actuators foropening and closing the valves in the cartridge of FIG. 1. FIG. 20 alsoshows a pressure delivery nozzle sealed to a pressure port formed in thecartridge of FIG. 1.

FIG. 21 is a partially exploded, isometric view of a reaction vessel ofthe cartridge of FIG. 1.

FIG. 22 is a front view of the vessel of FIG. 21.

FIG. 23 is a side view of the vessel of FIG. 21 inserted between twoheater plates.

FIG. 24 is a front view of one of the heater plates of FIG. 23.

FIG. 25 is a front view of an alternative reaction vessel according tothe present invention.

FIG. 26 is a front view of another reaction vessel according to thepresent invention.

FIG. 27 is another front view of the vessel of FIG. 21.

FIG. 28 is a front view of the vessel of FIG. 21 inserted into aheat-exchanging module of the instrument of FIG. 10.

FIG. 29 is an exploded view of a support structure for holding theplates of FIG. 23.

FIGS. 30-31 are assembled views of the support structure of FIG. 29.

FIG. 32 is an isometric view showing the exterior of one the opticsassemblies in the heat-exchanging module of FIG. 28.

FIG. 33 is an isometric view of the plates of FIG. 23 in contact withthe optics assembly of FIG. 32.

FIG. 34 is a partially cut away, isometric view of the reaction vesselof FIG. 21 inserted between the plates of FIG. 23. Only the lowerportion of the vessel is included in the figure.

FIG. 35 is a schematic block diagram of the electronics of theheat-exchanging module of FIG. 28.

DETAILED DESCRIPTION

The present invention provides an apparatus and method for analyzing afluid sample. In a first embodiment, the invention provides a cartridgefor separating a desired analyte from a fluid sample and for holding theanalyte for a chemical reaction. The fluid sample may be a solution orsuspension. In a particular use, the sample may be a bodily fluid (e.g.,blood, urine, saliva, sputum, seminal fluid, spinal fluid, mucus, orother bodily fluids). Alternatively, the sample may be a solid madesoluble or suspended in a liquid or the sample may be an environmentalsample such as ground or waste water, soil extracts, pesticide residues,or airborne spores placed in a fluid. Further, the sample may be mixedwith one or more chemicals, reagents, diluents, or buffers. The samplemay be pretreated, for example, mixed with chemicals, centrifuged,pelleted, etc., or the sample may be in a raw form.

The desired analyte is typically intracellular material (e.g., nucleicacid, proteins, carbohydrates, lipids, bacteria, or intracellularparasites). In a preferred use, the analyte is nucleic acid which thecartridge separates from the fluid sample and holds for amplification(e.g., using PCR) and optical detection. As used herein, the term“nucleic acid” refers to any synthetic or naturally occurring nucleicacid, such as DNA or RNA, in any possible configuration, i.e., in theform of double-stranded nucleic acid, single-stranded nucleic acid, orany combination thereof.

FIG. 1 shows an isometric view of a cartridge 20 according to thepreferred embodiment. The cartridge 20 is designed to separate nucleicacid from a fluid sample and to hold the nucleic acid for amplificationand detection. The cartridge 20 has a body comprising a top piece 22, amiddle piece 24, and a bottom piece 26. An inlet port for introducing afluid sample into the cartridge is formed in the top piece 22 and sealedby a cap 30. Six pressure ports 32 are also formed in the top piece 22.The pressure ports 32 are for receiving nozzles from pressure sources,e.g., pumps or vacuums. The cartridge also includes alignment legs 28extending from the bottom piece 26 for positioning the cartridge 20 inan instrument (described below with reference to FIG. 10). Indentationsor depressions 38A, 38B, and 38C are formed in the top and middle pieces22, 24. The indentations are for receiving optical sensors that detectfluid flow in the cartridge 20. The cartridge 20 further includes vents34, 36. Each pressure port and vent preferably includes a hydrophobicmembrane that allows the passage of gas but not liquid into or out ofthe vents and pressure ports. Modified acrylic copolymer membranes arecommercially available from, e.g., Gelman Sciences (Ann Arbor, Mich.)and particle-track etched polycarbonate membranes are available fromPoretics, Inc. (Livermore, Calif.).

FIG. 2 is an isometric view showing the underside of the cartridge 20.Nine holes 60 are formed in the bottom piece 26 for receiving valveactuators that open and close valves in the cartridge 20. A hole 62 isalso formed in the bottom piece 26 for receiving a transducer (describedin detail below with reference to FIG. 5). The cartridge 20 alsoincludes a reaction vessel 40 extending outwardly from the body of thecartridge. The vessel 40 has a reaction chamber 42 for holding areaction mixture (e.g., nucleic acid mixed with amplification reagentsand fluorescent probes) for chemical reaction and optical detection. Oneof the flow paths in the cartridge carries the reaction mixture to thechamber 42 for chemical reaction and optical detection. The vessel 40extends outwardly from the body of the cartridge 20 so that the vessel40 may be inserted between a pair of opposing thermal plates (forheating and cooling the chamber 42) without the need for decoupling thevessel 40 from the rest of the cartridge 20. This greatly reduces therisk of contamination and/or spilling. The vessel 40 may be integrallyformed with the body of the cartridge (e.g., integrally molded withmiddle piece 24). It is presently preferred, however, to produce thevessel 40 as a separate element that is coupled to the body duringmanufacture of the cartridge.

FIGS. 3-4 show exploded views of the cartridge. As shown in FIG. 3, themiddle piece 24 has multiple chambers formed therein. In particular, themiddle piece 24 includes a sample chamber 65 for holding a fluid sampleintroduced through the inlet port 64, a wash chamber 66 for holding awash solution, a reagent chamber 67 for holding a lysing reagent, awaste chamber 68 for receiving used sample and wash solution, aneutralizer chamber 70 for holding a neutralizer, and a master mixchamber 71 for holding a master mix (e.g., amplification reagents andfluorescent probes) and for mixing the reagents and probes with analyteseparated from the fluid sample. The sample chamber 65 optionallyincludes a side compartment 155 having slightly lower walls than thesample chamber 65. The side compartment 155 is for visually indicatingto a user when sufficient sample has been added to the sample chamber65, i.e., when the liquid level in the chamber 65 is high enough tospill over into the compartment 155.

The top piece 22 includes the vents 34, 36 and the six pressure ports32, as previously described. An elastomeric membrane or gasket 61 ispositioned and squeezed between the pieces 22, 24 to seal the variouschannels and chambers formed in the pieces. The middle piece 24preferably includes multiple sealing lips to ensure that the gasket 61forms an adequate seal. In particular, the middle piece 24 preferablyincludes sealing lips 73 surrounding each of the chambers 65, 66, 67,68, 70, and 71. The middle piece 24 also includes support walls 75around the perimeter, and intermediate sealing lips 76. The sealing lips73, 76 and support walls 75 locally compress the gasket 61 and achieve aseal.

As shown in FIG. 4, the middle piece 24 has formed in its undersidevarious channels, one of which leads to a lysing chamber 86. The chamber86 is aligned with the hole 62 in the bottom piece 26 so that atransducer (e.g., an ultrasonic horn) may be inserted through the hole62 to generate pressure waves in the lysing chamber 86. The middle piece24 also has nine valve seats 84 formed in its bottom surface. The valveseats 84 are aligned with the nine holes 60 in the bottom piece 26 sothat valve actuators may be inserted through the holes 60 into the valveseats 84.

An elastomeric membrane or gasket 61 is positioned and squeezed betweenthe pieces 24, 26 to seal the various channels, valve seats, and chamberformed in the middle piece 24. The middle piece 24 preferably includesmultiple sealing lips to ensure that the gasket 63 forms an adequateseal. In particular, the middle piece 24 preferably includes sealinglips 73 surrounding the lysing chamber 86, valve seats 84, and variouschannels. The middle piece 24 also includes support walls 75 around itsperimeter, and intermediate sealing lips 76. The sealing lips 73, 76 andsupport walls 75 locally compress the gasket 63 and achieve a seal. Inaddition to sealing various channels and chambers, the gasket 63 alsofunctions as a valve stem by compressing, when actuated through one ofthe holes 60, into a corresponding valve s eat 84, thus shutting one ofthe flow channels in the middle piece 24. This valve action is discussedin greater detail below with reference to FIGS. 15-16.

The gasket 63 also forms the bottom wall of the lysing chamber 86against which a transducer is placed to effect disruption of cells orviruses in the chamber 86. Each of the gaskets 61, 63 is preferablycomposed of an elastomer. Suitable gasket materials are silicone rubber,neoprene, EPDM, or any other compliant material. Each of the gaskets 61,63 preferably has a thickness in the range of 0.005 to 0.125 inches(0.125 to 3.175 mm), and more preferably in the range of 0.01 to 0.06inches (0.25 to 1.5 mm), with a presently preferred thickness of 0.031inches (0.79 mm). The thickness is selected to ensure that the gasket issufficiently compliant to seal the channels and chambers, to compressinto the valve seats 84 when forced, and to expand under pressure tocontact the transducer.

As shown in FIG. 3, the middle piece 24 includes a slot 79 through whichthe reaction vessel 40 is inserted during assembly of the cartridge. Thevessel 40 has two fluid ports 41, 43 for adding and removing fluid fromthe vessel. When the top piece 22 is sealed to the middle piece 24 viathe gasket 61, the ports 41, 43 are placed into fluidic communicationwith channels 80, 81, respectively, that are formed in the top piece 22(see FIG. 4). The gasket 61 seals the respective fluidic interfacesbetween the ports 41, 43 and the channels 80, 81. The top, middle, andbottom pieces 22, 24, 26 are preferably injection molded parts made of apolymeric material such as polypropylene, polycarbonate, or acrylic.Although molding is preferred for mass production, it also possible tomachine the top, middle, and bottom pieces 22, 24, 26. The pieces 22,24, 26 may be held together by screws or fasteners. Alternatively,ultrasonic bonding, solvent bonding, or snap fit designs could be usedto assemble the cartridge.

FIG. 4 also shows a filter ring 88. The filter ring 88 compresses andholds a stack of filters in the lysing chamber 86. FIG. 6 shows anexploded view of a filter stack 87. The purpose of the filter stack 87is to capture cells or viruses from a fluid sample as the sample flowsthrough the lysing chamber 86. The captured cells or viruses are thendisrupted (lysed) in the chamber 86. The cells may be animal or plantcells, spores, bacteria, or microorganisms. The viruses may be any typeof infective agents having a protein coat surrounding an RNA or DNAcore.

The filter stack 87 comprises a gasket 93, a first filter 94, a gasket95, a second filter 97 having a smaller pore size than the first filter94, a gasket 98, a third filter 100 having a smaller pore size than thesecond filter 97, a gasket 101, a woven mesh 102, and a gasket 103. Thefilter stack also preferably includes a first set of beads 96 disposedbetween the first and second filters 94 and 97 and a second set of beads99 disposed between the second and third filters 97 and 100. The filterring 88 compresses the filter stack 87 into the lysing chamber 86 sothat the gasket 93 is pressed against the filter 94, the filter 94 ispressed against the gasket 95, the gasket 95 is pressed against thefilter 97, the filter 97 is pressed against the gasket 98, the gasket 98is pressed against the filter 100, the filter 100 is pressed against thegasket 101, the gasket 101 is pressed against the mesh 102, the mesh 102is pressed against the gasket 103, and the gasket 103 is pressed againstthe outer perimeter of the bottom wall of the lysing chamber 86. Thegasket 95 is thicker than the average diameter of the beads 96 so thatthe beads are free to move in the space between the filters 94 and 97.Similarly, the gasket 98 is thicker than the average diameter of thebeads 99 so that the beads 99 are free to move in the space between thefilters 97 and 100. A fluid sample flowing through the channel 106 intothe lysing chamber 86 first flows through filter 94, then through filter97, next through filter 100, and lastly through the mesh 102. Afterflowing through the filter stack 87, the sample flows along flow ribs 91formed in the top of the lysing chamber 86 and through an outlet channel(not shown in FIG. 6).

Referring to FIG. 5, the cells or viruses captured in the filter stack(not shown in FIG. 5 for illustrative clarity) are lysed by coupling atransducer 92 (e.g., an ultrasonic horn) directly to the wall of thelysing chamber 86. In this embodiment, the wall of the lysing chamber 86is formed by the flexible gasket 63. The transducer 92 should directlycontact an external surface of the wall. The term “external surface” isintended to mean a surface of the wall that is external to the lysingchamber 86. The transducer 92 is a vibrating or oscillating device thatis activated to generate pressure waves in the chamber 86. The pressurewaves agitate the beads 96, 99 (FIG. 6), and the movement of the beadsruptures the captured cells or viruses. In general, the transducer forcontacting the wall of the lysing chamber 86 may be an ultrasonic,piezoelectric, magnetostrictive, or electrostatic transducer. Thetransducer may also be an electromagnetic device having a wound coil,such as a voice coil motor or a solenoid device. It is presentlypreferred that the actuator be an ultrasonic transducer, such as anultrasonic horn. Suitable horns are commercially available from Sonics &Materials, Inc. having an office at 53 Church Hill, Newton, Conn.06470-1614 USA. Alternatively, the ultrasonic transducer may comprise apiezoelectric disk or any other type of ultrasonic transducer that maybe coupled to the container. It is presently preferred to use anultrasonic horn because the horn structure is highly resonant andprovides for repeatable and sharp frequency of excitation and largemotion of the horn tip.

As previously described in FIG. 6, the filter stack includes a gasket atboth of its ends. As shown in FIG. 5, the middle cartridge piece 24 hasa sealing lip 90 against which the gasket at one end of the filter stackis compressed. The gasket at the other end of the filter stack iscompressed by the filter ring 88 to form a seal. The gasket material mayexpand into the relief area outside of the sealing lip 90. The width ofthe sealing lip 90 is small (typically 0.5 mm) so that an excessiveamount of force is not required to achieve a sufficient seal.

The filter ring 88 is held between the filter stack and the cartridgegasket 63. The cartridge gasket 63 is held between the middle piece 24and the bottom piece 26 by a sealing lip 406. Force is thereforetransferred from the bottom piece 26 through the gasket 63 to the filterring 88 and finally to the filter stack. The filter ring 88 contains acontact lip 404 that contacts the gasket 63. The contact lip 404 is nota primary sealing lip (though it will seal) but a force transfermechanism. The width of the contact lip 404 is larger than the width ofthe sealing lip 90 to ensure that deformation and sealing action occursin the filter stack and not taken up in squeezing the cartridge gasket63. The cartridge middle piece 24 also has a sealing lip 406 thatsurrounds the filter ring 88. This is an active sealing area that shouldnot be compromised by the presence of the filter ring 88. For thisreason, there is a gap 407 between the sealing lip 406 and the contactlip 404 on the filter ring 88. The gap 407 is provided to allow thegasket 63 to extrude into the gap 407 as it is compressed by the sealinglip 406 and the contact lip 404. If the contact lip 404 comes to adifferent elevation than the sealing lip 406, the seal will not becompromised id because of the gap 407 and the distance between the lips404 and 406.

Referring again to FIG. 6, the filter stack 87 is effective forcapturing cells or viruses as a fluid sample flows through the stack 87without clogging of any of the filters 94, 97, 100 in the stack. Thefirst filter 94 (having the largest pore size) filters out coarsematerial such as salt crystals, cellular debris, hair, tissue, etc. Thesecond filter 97 (having the medium pore size) captures cells or virusesin the fluid sample. The third filter 100 (having the smallest poresize) captures smaller cells or viruses in the sample. The filter stack87 thus enables the simultaneous capture of differently sized samplecomponents without clogging of the filters. The average pore size of thefirst filter 94 is selected to be small enough to filter coarse materialfrom the fluid sample (e.g. salt 1crystals, cellular debris, hair,tissue) yet large enough to allow the passage of the target cells orviruses containing the desired analyte (e.g., nucleic acid orproteins)m. In general, the pore size of the first filter 94 should bein the range of about 2 to 25 μm, with a presently preferred pore sizeof about 5 μm.

The average pore sizes of the second and third filters are selected independence upon the average size of the target cells o r viruses thatcontain the desired analyte(s). For example, in one embodiment, thefilter stack 87 is used to capture gonorrhea (GC) and chlamydia (Ct)organisms to determine the presnce of the diseases in the fluid sample.The GC and Ct organisms have different average diameters, about 1 to 2μm for GC organisms and about 0.3 μm for Ct organisms. In thisembodiment, the second filter 97 has an average pore size of about 1.2μm while the third filter 1or has an average pore size of about 0.22 μmso that most of the GC organisms are captured by the second filter 97while most of the Ct organisms are captured by the third filter 100. Thefilter stack thus enables the simultaneous capture of differently sizedtarget organisms and does so without clogging of the filters. The poresizes of the filters 97, 100 may be selected to capture desired cells orviruses of any size, and the scope of the invention is not limited tothe specific example given.

The filter stack 87 is also useful for disrupting the captured cells orviruses to release the intracellular material (e.g., nucleic acid)therefrom. The first and second sets of beads 96, 99 serve two usefulpurposes in this regard. First, the beads are agitated by the pressurewaves generated by the transducer. The movement of the beads rupturesthe captured cells or viruses. Second, the beads may shear the nucleicacid released from the lysed cells or viruses so that the strands ofnucleic acid are sufficiently short to flow through the filters and outof the lysing chamber 86. Suitable beads for rupturing cells or virusesinclude borosilicate glass, lime glass, silica, and polystyrene beads.

The beads may be porous or non-porous and preferably have an averagediameter in the range of 1 to 200 μm. The average diameter of the beads96, 99 is selected in dependence upon the intended target cells orviruses to be ruptured by the beads. The average diameter of the beads96 in the first set may be equal to the average diameter of the beads 99in the second set. Alternatively, when the first set of beads 96 is usedto rupture a type of target cell or virus that differs from the type ofcell or virus to be ruptured by the second set of beads 99, it isadvantageous to select the average diameter of the beads such that theaverage diameter of the beads 96 in the first set differs from theaverage diameter of the beads 99 in the second set. For example, whenthe filter stack is used to capture GC and Ct cells as described above,the beads 96 are 20 μm diameter borosilicate glass beads for rupturingthe GC organisms and the beads 99 are 106 μm diameter soda lime glassbeads for rupturing the Ct organisms. Each of the silicone gaskets 95,98 should be sufficiently thick to allow room for the beads 96, 99 tomove and rupture the cells or viruses.

The mesh 102 also serves two useful purposes. First the mesh providessupport to the filter stack 87. Second, the mesh breaks up air bubblesso that the bubbles can be channeled through the flow ribs 91 and out ofthe lysing chamber 86. To effectively break up or reduce the size of theair bubbles, the mesh 102 preferably has a small pore size. Preferably,it is a woven polypropylene mesh having an average pore size of about 25μm. To ensure that the air bubbles can escape from the lysing chamber86, it is desirable to use the cartridge in an orientation in whichliquid flows up (relative to gravity) through the filter stack 87 andthe lysing chamber 86. The upward flow through the chamber 86 aids theflow of air bubbles out of the chamber 86. Thus, the inlet port forentry of fluids into the chamber 86 should generally be at the lowestpoint in the chamber, while the exit port should be at the highest.

Many different embodiments of the filter stack are possible. Forexample, in one alternative embodiment, the filter stack has only twofilters and one set of beads disposed between the filters. The firstfilter has the largest pore size (e.g., 5 μm) and filters out coarsematerial such as salt crystals, cellular debris, hair, tissue, etc. Thesecond filter has a pore size smaller than the first filter and slightlysmaller than the target cells or viruses to be captured. Such a filterstack is described below with reference to FIG. 38. In anotherembodiment of the cartridge, the filter having the largest pore size(for filtering the coarse material) is positioned in a filter chamber(not shown) that is positioned upstream of the lysing chamber 86. Achannel connects to the filter chamber to the lysing chamber 86. In thisembodiment, a fluid sample flows first through the coarse filter in thefilter chamber and then through a second filter in the lysing chamber totrap the target cells or viruses in the lysing chamber.

Further, the beads in the filter stack may have a binding affinity fortarget cells or viruses in the fluid sample to facilitate capture of thetarget cells or viruses. For example, antibodies or certain receptorsmay be coated onto the surface of the beads to bind target cells in thesample. Moreover, the lysing chamber 86 may contain two different typesof beads for interacting with target cells or viruses. For example, thelysing chamber may contain a first set of beads coated with antibodiesor receptors for binding target cells or viruses and a second set ofbeads (intermixed with the first set) for rupturing the captured cellsor viruses. The beads in the lysing chamber 86 may also have a bindingaffinity for the intracellusar material (e.g., nucleic acid) releasedfrom the ruptured cells or viruses. Such beads are useful for isolatingtarget nucleic acid for subsequent elution and analysis. For example,the lysing chamber may contain silica beads to isolate DNA or cellulosebeads with oligo dT to isolate messenger PNA for RT-PCR. The lysingchamber 86 may also contain beads for removing unwanted material (e.g.,proteins, peptides) or chemicals (e.g., salts, metal ions, ordetergents) from the sample that might inhibit PCR. For example, thechamber 86 may contain ion exchange beads for removing proteins.Alternatively beads having metal ion chelators such as iminodiaceticacid will remove metal ions from biological samples.

FIGS. 21-22 illustrate the reaction vessel 40 in greater detail. FIG. 21shows a partially exploded view of the vessel 40, and FIG. 22 shows afront view of the vessel 40. The vessel 40 includes the reaction chamber42 (diamond-shaped in this embodiment) for holding a reaction Mixture.The vessel 40 is designed for optimal heat transfer to and from thereaction mixture and for efficient optical viewing of the mixture. Thethin shape of the vessel contributes to optimal thermal kinetics byproviding large surfaces for thermal conduction and for contactingthermal plates. In addition, the walls of the vessel provide opticalwindows into the chamber 42 so that the entire reaction mixture can beoptically interrogated. In more detail to FIGS. 21-22, the reactionvessel 40 includes a rigid frame 46 that defines the side walls 57A,57B, 59A, 59B of the reaction chamber 42. The frame 46 also defines aninlet port 41 and a channel 50 connecting the port 41 to the chamber 42.The frame 46 also defines an outlet port 43 and a channel 52 connectingthe port 43 to the chamber 42. The inlet port 41 and channel 50 are usedto add fluid to the chamber 42, and the channel 52 and outlet port 43are used for exit of fluid from the chamber 42. Alignment prongs 44A,44B are used to position the vessel 40 correctly during assembly of thecartridge.

As shown in FIG. 21, the vessel 40 also includes thin, flexible sheetsattached to opposite sides of the rigid frame 46 to form opposing majorwalls 48 of the chamber. (The major walls 48 are shown in FIG. 1exploded from the rigid frame 46 for illustrative clarity). The reactionchamber 42 is thus defined by the rigid side walls 57A, 57B, 59A, 59B ofthe frame 46 and by the opposing major walls 48. The opposing majorwalls 48 are sealed to opposite sides of the frame 46 such that the sidewalls 57A, 57B, 59A, 59B connect the major walls 48 to each other. Thewalls 48 facilitate optimal thermal conductance to the reaction mixturecontained in the chamber 42. Each of the walls 48 is sufficientlyflexible to contact and conform to a respective thermal surface, thusproviding for optimal thermal contact and heat transfer between thethermal surface and the reaction mixture contained in the chamber 42.Furthermore, the flexible walls 48 continue to conform to the thermalsurfaces if the shape of the surfaces changes due to thermal expansionor contraction during the course of the heat-exchanging operation.

As shown in FIG. 23, the thermal surfaces for contacting the flexiblewalls 48 are preferably formed by a pair of opposing plates 190A, 190Bpositioned to receive the chamber 42 between them. When the chamber 42of the vessel 40 is inserted between the plates 190A, 190B, the innersurfaces of the plates contact the walls 48 and the flexible wallsconform to the surfaces of the plates. The plates are preferably spaceda distance from each other equal to the thickness T of the chamber 42 asdefined by the thickness of the frame 46. In this position, minimal orno gaps are found between the plate surfaces and the walls 48. Theplates may be heated and cooled by various thermal elements to inducetemperature changes within the chamber 42, as is described in greaterdetail below.

The walls 48 are preferably flexible films of polymeric material such aspolypropylene, polyethylene, polyester, or other polymers. The films mayeither be layered, e.g., laminates, or the films may be homogeneous.Layered films are preferred because they generally have better strengthand structural integrity than homogeneous films. In particular, layeredpolypropylene films are presently preferred because polypropylene is notinhibitory to PCR. Alternatively, the walls 48 may comprise any othermaterial that may be formed into a thin, flexible sheet and that permitsrapid heat transfer. For good thermal conductance, the thickness of eachwall 48 is preferably between about 0.003 to 0.5 mm, more preferablybetween 0.01 to 0.15 mm, and most preferably between 0.025 to 0.08 mm.

Referring again to FIG. 22, the vessel 40 also preferably includesoptical windows for in situ optical interrogation of the reactionmixture in the chamber 42. In the preferred embodiment, the opticalwindows are the side walls 57A, 57B of the rigid frame 46. The sidewalls 57A, 57B are optically transmissive to permit excitation of thereaction mixture in the chamber 42 through the side wall 57A anddetection of light emitted from the chamber 42 through the side wall57B. Arrows A represent illumination beams entering the chamber 42through the side wall 57A and arrows B represent emitted light (e.g.,fluorescent emission from labeled analytes in the reaction mixture)exiting the chamber 42 through the side wall 57B.

The side walls 57A, 57B are preferably angularly offset from each other.It is usually preferred that the walls 57A, 57B are offset from eachother by an angle of about 90°. A 90° angle between excitation anddetection paths assures that a minimum amount of excitation radiationentering through the wall 57A will exit through wall 57B. In addition,the 90° angle permits a maximum amount of emitted light (e.g.fluorescence) to be collected through wall 57B. The walls 57A, 57B arepreferably joined to each other to form a “V”, shaped intersection atthe bottom of the chamber 42. Alternatively, the angled walls 57A, 57Bneed not be directly joined to each other, but may be separated by anintermediary portion, such as another wall or various mechanical orfluidic features which do not interfere with the thermal and opticalperformance of the vessel. For example, the walls 57A, 57B may meet at aport which leads to another processing area in communication with thechamber 42, such as an integrated capillary electrophoresis area. In thepresently preferred embodiment, a locating tab 58 extends from the frame46 below the intersection of walls 57A, 57B. The tab 58 is used toproperly position the vessel 40 in a heat-exchanging module describedbelow with reference to FIG. 28.

Optimum optical sensitivity may be attained by maximizing the opticalpath length of the light beams exciting the labeled analyte in thereaction mixture and the emitted light that is detected, as representedby the equation:

I _(o) /I _(i) =C*L*A,

where I_(o) is the illumination output of the emitted light in volts,photons or the like, C is the concentration of analyte to be detected,I_(i) is the input illumination, L is the path length, and A is theintrinsic absorptivity of the dye used to label the analyte.

The thin, flat reaction vessel 40 of the present invention optimizesdetection sensitivity by providing maximum optical path length per unitanalyte volume. Referring to FIGS. 23 and 27, the vessel 40 ispreferably constructed such that each of the sides walls 57A, 57B, 59A,59B of the chamber 42 has a length L in the range of 1 to 15 mm, thechamber has a width W in the range of 1.4 to 20 mm, the chamber has athickness T in the range of 0.5 to 5 mm, and the ratio of the width W ofthe chamber to the thickness T of the chamber is at least 2:1. Theseparameters are presently preferred to provide a vessel having arelatively large average optical path length through the chamber, i.e. 1to 15 mm on average, while still keeping the chamber sufficiently thinto allow for extremely rapid heating and cooling of the reaction mixturecontained therein. The average optical path length of the chamber 42 isthe distance from the center of the side wall 57A to the center of thechamber 42 plus the distance from the center of the chamber 42 to thecenter of the side wall 57B.

More preferably, the vessel 40 is constructed such that each of thesides walls 57A, 57B, 59A, 59B of the chamber 42 has a length L in therange of 5 to 12 mm, the chamber has a width W in the range of 7 to 17mm, the chamber has a thickness T in the range of 0.5 to 2 mm, and theratio of the width W of the chamber to the thickness T of the chamber isat least 4:1. These ranges are more preferable because they provide avessel having both a larger average optical path length (i.e., 5 to 12mm) and a volume capacity in the range of 12 to 100 μl while stillmaintaining a chamber sufficiently thin to permit extremely rapidheating and cooling of a reaction mixture. The relatively large volumecapacity provides for increased sensitivity in the detection of lowconcentration analytes, such as nucleic acids.

In the preferred embodiment, the reaction vessel 40 has a diamond-shapedchamber 42 defined by the side walls 57A, 57B, 59A, 59B, each of theside walls has a length of about 10 mm, the chamber has a width of about14 mm, the chamber has a thickness T of 1 mm as defined by the thicknessof the frame 46, and the chamber has a volume capacity of about 100 μl.This reaction vessel provides a relatively large average optical pathlength of 10 mm through the chamber 42. Additionally, the thin chamberallows for extremely rapid heating and/or cooling of the reactionmixture contained therein. The diamond-shape of the chamber 42 helpsprevent air bubbles from forming in the chamber as it is filled with thereaction mixture and also aids in optical interrogation of the mixture.

Referring again to FIG. 22, the frame 46 is preferably made of anoptically transmissive material, e.g., a polycarbonate or clarifiedpolypropylene, so that the side walls 57A, 57B are opticallytransmissive. As used herein, the term optically transmissive means thatone or more wavelengths of light may be transmitted through the walls.

In the preferred embodiment, the optically transmissive walls 57A, 57Bare substantially transparent. In addition, one or more optical elementsmay be present on the optically transmissive side walls 57A, 57B. Theoptical elements may be designed, for example, to maximize the totalvolume of solution which is illuminated by a light source, to focusexcitation light on a specific region of the chamber 42, or to collectas much fluorescence signal from as large a fraction of the chambervolume as possible. In alternative embodiments, the optical elements maycomprise gratings for selecting specific wavelengths, filters forallowing only certain wavelengths to pass, or colored lenses to providefiltering functions. The wall surfaces may be coated or comprisematerials such as liquid crystal for augmenting the absorption ofcertain wavelengths. In the presently preferred embodiment, theoptically transmissive walls 57A, 57B are substantially clear, flatwindows having a thickness of about 1 mm.

The side walls 59A, 59B preferably includes reflective faces 56 whichinternally reflect light trying to exit the chamber 42 through the sidewalls 59A, 59B. The reflective faces 56 are arranged such that adjacentfaces are angularly offset from each other by about 90°. In addition,the frame 46 defines open spaces between the side walls 59A, 59B and thesupport ribs 53. The open spaces are occupied by ambient air that has adifferent refractive index than the material composing the frame (e.g.,plastic). Due to the difference in the refractive indexes, thereflective faces 56 are effective for internally reflecting light tryingto exit the chamber through the walls 59A, 59B and provide for increaseddetection of optical signal through the walls 57A, 57B. Preferably, theoptically transmissive side walls 57A, 57B define the bottom portion ofthe diamond-shaped chamber 42, and the retro-reflective side walls 59A,59B define the top portion of the chamber.

A preferred method for fabricating the reaction vessel 40 will now bedescribed with reference to FIGS. 21-22. The reaction vessel 40 may befabricated by first molding the rigid frame 46 using known injectionmolding techniques. The frame 46 is preferably molded as a single pieceof polymeric material, e.g., clarified polypropylene. After the frame 46is produced, thin, flexible sheets are cut to size and sealed toopposite sides of the frame 46 to form the major walls 48 of the chamber42. The major walls 48 are preferably cast or extruded films ofpolymeric material, e.g., polypropylene films, that are cut to size andattached to the frame 46 using the following procedure. A first piece offilm is placed over one side of the frame 46. The frame 46 preferablyincludes a tack bar 47 for aligning the top edge of the film. The filmis placed over the bottom portion of the frame 46 such that the top edgeof the film is aligned with the tack bar 47 and such that the filmcompletely covers the bottom portion of the frame 46 below the tack bar47. The film should be larger than the bottom portion of the frame 46 sothat it may be easily held and stretched flat across the frame. The filmis then cut to size to match the outline of the frame by clamping to theframe the portion of the film that covers the frame and cutting away theportions of the film that extend past the perimeter of the frame using,e.g., a laser or die.

The film is then tack welded to the frame, preferably using a laser.

The film is then sealed to the frame 46, preferably by heat sealing.Heat sealing is presently preferred because it produces a strong sealwithout introducing potential contaminants to the vessel as the use ofadhesive or solvent bonding techniques might do. Heat sealing is alsosimple and inexpensive. The heat sealing may be performed using, e.g., aheated platen. An identical procedure may be used to cut and seal asecond sheet to the opposite side of the frame 46 to complete thechamber 42. Many variations to this fabrication procedure are possible.For example, in an alternative embodiment, the film is stretched acrossthe bottom portion of the frame 46 and then sealed to the 42 frame priorto cutting the film to size; After sealing the film to the frame, theportions of the film that extend past the perimeter of the frame are cutaway using, e.g., a laser or die.

Although it is presently preferred to mold the frame 46 as a singlepiece, it is also possible to fabricate the frame from multiple pieces.For example, the side walls 57A, 57B forming the angled optical windowsmay be molded from polycarbonate, which has good optical transparency,while the rest of the frame is molded from polypropylene, which isinexpensive and compatible with PCR. The separate pieces can be attachedtogether in a secondary step. For example, the side walls 57A, 57B maybe press-fitted and/or bonded to the remaining portion of the frame 46.The flexible walls 48 may then be attached to opposite sides of theframe 46 as previously described.

Referring again to FIG. 3, it is presently preferred to use a gasket 61to seal the ports 41, 43 of the vessel 40 to corresponding channels 80,81 (FIG. 4) in the cartridge body. Alternatively, fluidic seals may beestablished using a luer fitting, compression fitting, or swagedfitting. In another embodiment, the cartridge body and frame of thevessel 40 are molded as a single part, and the flexible major walls ofthe vessel are heat-sealed to opposite sides of the frame.

Referring again to FIG. 22, the chamber 42 is filled by forcing liquid(e.g., a reaction mixture) to flow through the port 41 and the channel50 into the chamber 42. The liquid may be forced to flow into thechamber 42 using differential pressure (i.e., either pushing the liquidaft through the inlet port 41 or aspirating the liquid by applying avacuum to the outlet port 43). As the liquid fills the chamber 42, itdisplaces air in the chamber. The displaced air exits the chamber 42through the channel 52 and the port 43. For optimal detection of analytein the chamber 42, the chamber should not contain air bubbles. To helpprevent the trapping of air bubbles in the chamber 42, the connectionbetween the chamber 42 and the outlet channel 52 should be at thehighest point (with respect to gravity) in the chamber 42. This allowsair bubbles in the chamber 42 to escape without being trapped. Thus, thevessel 40 is designed to be used in the vertical orientation shown inFIG. 22.

FIG. 25 shows another vessel 206 designed to be used in a horizontalorientation. The vessel 206 has an inlet port 41 and an inlet channel 50connecting the inlet port 41 to the bottom of the chamber 42. The vesselalso has an outlet port 43 and an outlet channel 52 connecting theoutlet port 43 to the top of the chamber 42. Thus, any air bubbles inthe chamber 42 may escape through the outlet channel 52 without becomingtrapped. FIG. 26 shows another vessel 207 having two inlet ports 41, 45and one outlet port 43. Inlet channels 50, 54 connect the respectiveinlet ports 41, 45 to the chamber 42, and outlet channel 52 connects thechamber 42 to outlet port 43. Many other different embodiments of thevessel are also possible. In each embodiment, it is desirable toevacuate the chamber 42 from the highest point (with respect to gravity)in the chamber and to introduce liquid into the chamber from a lowerpoint.

FIGS. 15A-15B illustrate two types of valves used in the cartridge. Asshown in FIG. 15A, there are two types of fundamental concepts to thevalve action, and hence two types of valves. The first valve uses acone-shaped or conical valve seat 160 formed in the middle cartridgepiece 24. The valve seat 160 is a depression, recess, or cavity moldedor machined in the middle piece 24. The valve seat 160 is in fluidcommunication with a chamber 167 through a port or channel 157 thatintersects the center of the conical valve seat 160. As shown in FIG.15B, a valve actuator 164A having a spherical surface is forced againstthe elastic membrane 63 and into the valve seat 160, establishing acircular ring of contact between the membrane 63 and the valve seat 160.The kinematic principle is that of a ball seated into a cone. Thecircular seal formed by the membrane 63 and valve seat 160 prevents flowbetween the channel 157 (and hence the chamber 167) and a side channel158 extending from a side of the valve seat 160. The side channel 158 isdefined by the membrane 63 and the middle cartridge piece 24.

As shown in FIG. 15A, the other type of valve controls the cross flowbetween the channel 158 and another side channel 159 formed between themembrane 63 and the middle cartridge piece 24. In this case, a circularring of contact would be ineffective. Instead, the second valvecomprises a recess depression or cavity 161 formed in the middlecartridge piece 24. The cavity 161 separates the channels 158, 159 fromeach other. An end of the channel 158 is positioned on one side of thecavity 161, and an end of the channel 159 is positioned on the oppositeside of the cavity 161. The cavity 161 is defined by a first curvedsurface 162A positioned adjacent the end of the channel 158, a secondcurved surface 162B positioned adjacent the end of the channel 159, anda third surface 163 between the first and second curved surfaces 162A,1628. As shown in FIG. 15B, the curved surfaces provide two valve seatsthat are the primary contact area for the membrane 63 to seal off theflow between the channels 158 and 159. The kinematic principle is thatof a ball (or spherical end on a valve actuator) held by three contactpoints, the upward force on the actuator and the two valve seats 162A,162B.

As shown in FIG. 16A, the first and second curved surfaces 162A, 162Bare preferably concentric spherical surfaces. The valve actuator 164 hasalso has a spherical surface for pressing the membrane 63 tightlyagainst the surfaces 162A, 162B. In addition, each of the surfaces 162A,162B preferably has a spherical radius of curvature R1 equal to thecombined radius of curvature R2 of the valve actuator 164 plus thethickness T of the membrane 63. For example, if the radius of curvatureR2 of the surface of the valve actuator 164 is 0.094 inches and themembrane 63 has a thickness T of 0.031 inches; then the radius ofcurvature R1 of each of the surfaces 162A, 162B is 0.125 inches. Ingeneral, the size and radius of curvature of the valve seats isdependent upon the size of the channels in the cartridge. The valves arepreferably made just large enough to effectively seal the channels butno larger so that dead volume in the cartridge is minimized.

As shown in FIG. 16B, the third surface 163 is recessed from the firstand second surfaces 162A, 162B to provide a gap 166 between the membrane63 and the third surface 163 when the membrane 63 is pressed against thefirst and second surfaces 162A, 162B. Stated another way, the surfaces162A, 162B are raised or elevated from the surface 163. The gap 166ensures that the membrane 63 contacts primarily the valve seats 162A,162B rather than the entire surface of the cavity 161 so that maximumpressure is applied to the valve seats 162A and 162B by the membrane 63.This provides a very strong seal with minimal actuator force required.

Referring again to FIG. 15B, in both types of valves the respectivekinematic principle defines the location of the mating parts. In boththe ball-in-cone concept and the ball-against-two-spherical-surfacesconcept, the ball or spherical shaped valve actuator is permitted toseek its own location as it is forced against the valve seat(s).

There is a deliberate clearance (e.g., 0.01 to 0.03 inches) between thevalve actuator and the hole in the bottom cartridge piece 26 in whichthe actuator 164 travels so that only the valve seat action defines thelocation of the mating pieces.

The valve actuators can be controlled by a variety of mechanisms. FIGS.17-19 illustrate one such mechanism. As shown in FIG. 17, a valveactuator 172 has a spherical surface for pressing the gasket 63 into avalve seat. The actuator 172 also has a flange 177 on its bottomportion. The cartridge includes an elastic body, such as a spring 174,that pushes against a ledge in the lower cartridge piece 26 to bias thevalve actuator against the gasket 63. The spring 174 is sufficientlystrong to close the valve unless a deliberate force is applied to pulldown the actuator 172. The valves in the cartridge may be kept closed inthis manner for shipping and storage before the cartridge is used. Thus,the cartridge may be preloaded during manufacture with the necessaryreagents and wash solutions to analyze a fluid sample without the fluidsleaking out of the cartridge during shipping and storage.

The actuator pull-down mechanism is usually located in an instrumentinto which the cartridge is placed for sample analysis (one suchinstrument is described in detail below with reference to FIG. 10). Themechanism comprises a sliding guide 175 that rotates a hinged pull-downmember 180 having a jaw 181 for receiving the flange 177 of the actuator172. As shown in FIG. 18, the sliding guide 175 rotates the hingedpull-down member 180 until the flange 177 is positioned within the jaw181. As shown in FIG. 19, a solenoid 146 pulls down the member 180 andthus the valve actuator 172 so that the gasket 63 is released from thevalve seat, thus opening the valve and permitting fluid flow between thechannels 170 and 171.

FIG. 20 illustrates the manner in which fluid flow into and out of thesample chamber, wash chamber, neutralizer chamber, and reagent chambersis controlled in the cartridge. Each of these chambers, as illustratedby a chamber 414 in FIG. 20, is covered by a hydrophobic membrane 410that allows the passage of gas but not liquid therethrough. Thehydrophobic membrane 410 is positioned between the chamber 414 and apressure port 32. The pressure port 32 is formed in the upper cartridgepiece 22 and positioned over the chamber 414. The membrane 410 holdsliquids in the chamber 414 during shipping and storage of the cartridge,even if the cartridge is turned upside down. The pressure port 32 issized to receive a pressure nozzle that is connected to a pressuresource (e.g., a vacuum or pneumatic pump) usually located in theexternal instrument. The nozzle 182 includes an o-ring 184 and a flange415. A spring 185 pushes against the flange 415 to force the nozzle 182into the pressure port 32 so that the o-ring 184 establishes a sealaround the port 32. In operation, positive air pressure or a vacuum isapplied to the chamber 414 through the pressure port 32 to force liquidsout of or into, respectively, the chamber 414.

A conical valve seat 160 (previously described with reference to FIGS.15A-15B) is formed in the middle cartridge piece 24 below the chamber414 to control the flow of liquid between the chamber 414 and aconnecting channel 411. The valve is opened and closed by a valveactuator 186 having a flange 187 and a spring 188 pressing against theflange 187 to hold the valve closed until a downward force is applied tothe actuator 186. The downward force is preferably supplied by asolenoid that pulls down the actuator 186 to open the valve. The valveactuator 186 and solenoid are preferably located in the instrument.

FIGS. 7-8 show top and bottom plan views, respectively, of thecartridge. FIG. 9 is a schematic block diagram of the cartridge. Asshown in any of FIGS. 7-9, the cartridge includes a sample chamber 65having a port for adding a fluid sample to the cartridge and a sampleflow path extending from the sample chamber.65. The sample flow pathextends from the sample chamber 65 through a valve 107 and into achannel 106. The channel 106 includes a sensor region 136 in which thechannel 106 has a flat bottom enabling easy optical detection of thepresence of liquid in the channel. The sample flow path continues fromthey channel 106 into the lysing chamber 86 and through the filter stack87. The sample flow path also includes a channel 109 for exit of fluidfrom the lysing chamber 86, a channel 110 having a flat-bottomeddetection region 137, a valve 111, and a channel 112 leading to thevented waste chamber 68 through a valve 114.

The cartridge also includes the wash chamber 66 for holding washsolution and the reagent chamber 67 for holding lysing reagent. The washchamber 66 is connected to the lysing chamber 86 through a valve 115,channel 117, and channel 106. The reagent chamber 67 is connected to thelysing chamber 86 through a valve 119, channel 117, and channel 106.Sample components (e.g., cells or viruses in the sample) are captured inthe filter stack 87 and lysed in the chamber 86 to release targetanalyte (e.g., nucleic acid) from the sample components. The cartridgealso includes an analyte flow path extending from the lysing chamber 86for carrying the analyte separated from the fluid sample to the reactionvessel 40 for chemical reaction and optical detection. The analyte flowpath extends from the chamber 86 through the channel 109, channel 110,and valve 111. After passing through the valve 111, the analyte flowpath diverges from the sample flow path. While the sample flow pathextends though channel 112 into the waste chamber 68, the analyte flowpath diverges into the U-shaped channel 122. The analyte flow path thenextends into and out of the neutralizer chamber 70 through a valve 124.The analyte flow path also passes into and out of the master mix chamber71 through a valve 126. From the master mix chamber 71, the analyte flowpath extends along the channel 122, through a valve 127, through channel80, and into the reaction vessel 40 through the port 41.

The reaction vessel 40 includes the port 41 for adding a reactionmixture to the vessel, and the port 43 for exit of fluids (e.g., air orexcess reaction mixture) from the vessel. The cartridge also includeschannel 81 in fluid communication with the port 43. The channel 81includes a flat-bottomed detection region 130 for detecting the presenceof liquid in the channel. The channel 81 connects to a channel 131(channel 131 extends straight down perpendicular to the page in the topplan view of FIG. 7).

Channel 131 connects to a channel 132 which in turn connects to achannel 134 through a valve 133 (channel 134 extends straight upperpendicular to the page in the top plan view of FIG. 7). The channel134 leads to the vent 36 which has a hydrophobic membrane to permit theescape of gas but not liquid from the cartridge. The channels, vent andvalve positioned downstream from the reaction vessel 40 are used topressurize the chamber 42 of the vessel, as is described in theoperation section below.

The cartridge also includes a first pressure port 105 positioned abovethe sample chamber 65, a second pressure port 116 positioned above thewash chamber 66, a third pressure port 118 positioned above the reagentchamber 67, a fourth pressure port 123 positioned above the neutralizerchamber 70, a fifth pressure port 125 positioned above the master mixchamber 71, and a sixth pressure port 128 positioned at the end of theU-shaped channel 122. The cartridge further includes sensor chambers 120and 121 in fluid communication with the waste chamber 68. The sensorchambers 120 and 121 indicate when predetermined volumes of liquid havebeen received in the waste chamber 68, as is described in detail below.

Referring to FIG. 10, the cartridge is preferably used in combinationwith an instrument 140 designed to accept one or more of the cartridges.For clarity of illustration, the instrument 140 shown in FIG. 10 acceptsjust one cartridge. It is to be understood, however, that the instrumentmay be designed to process multiple cartridges simultaneously. Theinstrument 140 includes a cartridge nest 141 into which the cartridge isplaced for processing.

The instrument 140 also includes the transducer 92 (e.g., an ultrasonichorn) for generating pressure waves in the lysing chamber of thecartridge, nine valve actuators 142 for actuating the nine valves in thecartridge, nine corresponding solenoids 146 for pulling down the valveactuators, and six pressure nozzles 145 for interfacing with sixcorresponding pressure ports formed in the cartridge. In addition, theinstrument includes or is connected to one or more regulated pressuresources for supplying pressure to the cartridge through the pressurenozzles 145. Suitable pressure sources include syringe pumps, compressedair sources, pneumatic pumps, or connections to external sources ofpressure. The instrument further includes three slotted optical sensors143 and three reflective optical sensors 144.

FIG. 13 illustrates the slotted optical sensors 143 positioned to detectliquid in the sensor chambers 120, 121 and in the reagent chamber 67.Each sensor 143 includes a built in LED and photodiode positioned onopposite sides of the sensor. The LED emits a beam that is detected bythe photodiode if the beam is not substantially refracted. Such slottedoptical sensors are commercially available from a number of suppliers.The cartridge is shaped so that the slotted optical sensors fit aroundthe chambers 67, 120, and 121. The operation of each sensor is asfollows. It liquid is not present in the chamber the sensor surrounds,the beam from the LED is substantially refracted by air in the chamberand the curved inner walls of the chamber and only a weak signal, ifany, is detected by the photodiode since air has an index of refractionthat does not closely match that of the plastic cartridge. If there isliquid present in the chamber, however, the beam from the LED does notrefract or is only slightly refracted and produces a much strongersignal detected by the photodiode since the liquid has an index ofrefraction closely matching that of the plastic cartridge. The opticalsensors 143 are therefore useful for determining the presence or absenceof liquid in the chambers 67, 120, and 121.

FIG. 14 shows a cut-away, schematic side view of the sensor chamber 120in fluid communication with the waste chamber 68 and surrounded by theslotted optical sensor 143. The sensor chamber 120 and sensor 143 areused to indicate when a predetermined volume of liquid is present in thewaste chamber 68. The sensor chamber 120 is partially separated from thewaste chamber 68 by a wall 151 having a spillover rim 152. The height ofthe wall is selected so that when the predetermined volume of liquid isreceived in the waste in chamber 68, the liquid spills over thespillover rim 152 and into the sensor chamber 120. The liquid in thesensor chamber 120 is then detected by the sensor 143.

Referring again to FIG. 13, the cartridge may also include a secondsensor chamber 121 in fluid communication with the waste chamber 68. Thesecond sensor chamber 121 is also separated from the waste chamber 68 bya wall 153 having a spillover rim. The wall 153 is taller than the wall152 so that liquid does not spill over the wall 153 until a secondpredetermined volume of fluid in addition to the first predeterminedvolume of fluid has been received in the waste chamber 68. The sensorchambers 120, 121 and the optical sensors 143 are useful for controllingthe operation of the cartridge. The height of the wall 152 is preferablyselected such that when a fixed volume of fluid sample from the samplechamber 65 has flowed through the sample flow path to the waste chamber68, the sample liquid spills over into the sensor chamber 120 and isdetected. The detection in chamber 120 triggers the release of washsolution from the wash chamber 66 which flows through the sample flowpath to the waste chamber 68. When an incremental volume of the washsolution is received in the chamber 68, liquid spills over the wall 153into the sensor chamber 121 and is detected. The detection of liquid inthe chamber 121 then triggers the release of lysing reagent from thechamber 67. The sensor 143 surrounding the chamber 67 may then be usedto indicate when the chamber 67 is empty, triggering the start ofultrasonic lysis. In an is alternative embodiment, the cartridge mayhave two waste chambers, one for sample and one for wash, with eachwaste chamber having a respective sensor chamber connected thereto.

In-line reflective optical sensors 144 are used to determine thepresence or absence of liquid in the flat-bottomed detection regions130, 136, 137, of channels 81, 106, and 110, respectively (FIG. 7). Eachsensor 144 has a built in emitter and detector that is positioned over aflat-bottomed detection region. The emitter emits a beam that isreflected from the cartridge and detected by the detector. The sensordetects a change in signal when as an air/liquid interface passesthrough the detection region. Optionally, dual emitter reflectiveoptical sensors may be used for a more reliable detection operation.Both types of reflective optical sensors are well known in the art andcommercially available.

Referring again to FIG. 10, the instrument 140 also includes aheat-exchanging module 147 having a slot 148 for receiving the reactionvessel of the cartridge. The module 147 is described in detail belowwith reference to FIG. 28. The instrument 140 further includes a latchmechanism 149 for latching a lid 150 over a cartridge. The cartridgenest 141 includes alignment holes 401 for receiving the legs of thecartridge. The alignment holes 401 ensure proper positioning of thecartridge in the nest 141 so that the pressure nozzles 145, transducer92, and valve actuators 142 fit into the corresponding ports in thecartridge and so that the reaction vessel fits into the slot 148. Thetransducer 92 should be positioned in the instrument 140 such that whenthe cartridge is placed in the nest 141, the transducer contacts thebottom wall of the lysing chamber 86, as shown in the cut-away view ofFIG. 5. In addition, the instrument may include a spring or similarmechanism to bias the transducer 92 against the wall of the lysingchamber 86.

The instrument 140 also includes various conventional equipment notshown in FIG. 10 including a main logic board having a microcontrollerfor controlling the operation of the solenoids 146, transducer 92,heat-exchanging module 147, and optical sensors 143, 144. The instrumentalso includes or is connected to a power supply for powering theinstrument and a pneumatic pump for supplying air pressure through thenozzles 145. The instrument 140 is preferably computer-controlled using,e.g., the microcontroller which is programmed to perform the functionsdescribed in the operation section below. Alternatively, the instrumentmay controlled by a separate computer, or controlled by a combination ofa separate computer and an on-board microcontroller.

FIG. 11 shows an isometric view of the cartridge 20 placed in theinstrument 140 for processing. FIG. 11 shows a partial cut-away view ofthe instrument 140 with the lid 150 closed. Referring again to FIG. 11,a memory or microprocessor chip may optionally be incorporated as partof the cartridge 20. This chip preferably contains information such asthe type of cartridge, program information such as specific protocolsfor the processing of the cartridge, tolerances for accept and reject,serial numbers and lot codes for quality tracking, and provision forstoring the results of the processing. Integrated electronic memory onthe cartridge 20 allows for rapid, easy, and error-free set-up of theinstrument 140 for different fluidic processing protocols. When thecartridge 20 is inserted into the instrument 140, the instrument mayelectronically address the memory on the cartridge, and thusautomatically receive the appropriate set of instructions forcontrolling the time-sequence of fluidic operations to be carried outwith the inserted cartridge. The instrument 140 may simply sequentiallyretrieve and execute each step in the cartridge's memory, or downloadits contents so that the user may edit the sequence using, e.g., thecontroller computer.

If suitable memory is included on the cartridge, such as writable memory(e.g., erasable programmable read-only memory (EPROM), electricallyerasable programmable read-only memory (EEPROM), etc., intermediate andfinal results, based on the sample introduced into the cartridge, couldbe written by the instrument into the cartridge's memory for co-locatedstorage with the physical sample after processing. This is particularlyadvantageous in applications where archiving of samples and results isnecessary, such as forensics. In addition, other information can bestored in the memory on the cartridge, in unalterable (or alterable)forms. For example, cartridge serial number, lot manufactureinformation, and related information could be pre-programmed andunalterable. User data, technician identification number, date of test,location of test and instrument serial number could be unalterablywritten into the cartridge. This allows for easy identification of the“chain of custody” in the handling of a specimen. Engineers skilled inthe art of data storage will recognize that other memory means thanelectronic can be used, such as optically-addressed printed regions(e.g., ink-jet or thermal), magnetic strips, etc.

FIG. 28 shows the heat-exchanging module 147 of the instrument intowhich the reaction vessel 40 is inserted for thermal processing andoptical detection of target analyte(s) in the reaction mixture. Themodule 147 preferably includes a housing 208 for holding the variouscomponents of the module. The module 147 also includes the thermalplates 190 described above. The housing 208 includes a slot (not shownin FIG. 28) above the plates 190 so that the reaction chamber of thevessel 40 may be inserted through the slot and between the plates. Theheat-exchanging module 147 also preferably includes a cooling system,such as a fan 212. The fan 212 is positioned to blow cooling air pastthe surfaces of the plates 190 to cool the plates and hence cool thereaction mixture in the vessel 40. The housing 208 preferably defineschannels for directing the cooling air past the plates 190 and out ofthe module 147.

The heat-exchanging module 147 further includes an optical excitationassembly 216 and an optical detection assembly 218 for opticallyinterrogating the reaction mixture contained in the vessel 40. Theexcitation assembly 216 includes a first circuit board 220 for holdingits electronic components, and the detection assembly 216 includes asecond circuit board 222 for holding its electronic components. Theexcitation assembly 216 includes one or more light sources (e.g., anLED. laser, or light bulb) for exciting fluorescently-labeled analytesin the vessel 40. The excitation assembly 216 also includes one or morelenses for collimating the light from the light sources, as well asfilters for selecting the excitation wavelength ranges of interest. Thedetection assembly 218 includes one or more detectors (e.g., aphotodiode, photomultiplier tube, or CCD) for detecting the lightemitted from the vessel 40. The detection assembly 218 also includes oneor more lenses for focusing and collimating the emitted light, as wellas filters for selecting the emission wavelength ranges of interest.Suitable optical excitation and detection assemblies for use in theheat-exchanging module 147 are described in International PublicationNumber WO 99/60380 (International Application Number PCT/US99/11182)published Nov. 25, 1999, the disclosure of which is incorporated byreference herein.

The optics assemblies 216, 218 are positioned in the housing 208 suchthat when the chamber of the vessel 40 is inserted between the plates190, the excitation assembly 216 is in optical communication with thechamber 42 through the optically transmissive side wall 57A (see FIG.22) and the detection assembly 218 is in optical communication with thechamber through the optically transmissive side wall 57B (FIG. 22). Inthe preferred embodiment, the optics assemblies 216, 218 are placed intooptical communication with the optically transmissive side walls bysimply locating the optics assemblies 216, 218 next to the bottom edgesof the plates 190 so that when the chamber of the vessel is placedbetween the plates, the optics assemblies 216, 218 directly contact, orare in close proximity to, the side walls.

FIG. 34 shows a partially cut-away, isometric view of the chamber of thevessel inserted between the plates 190A, 190B (the top portion of thevessel is cut away). The vessel preferably has an angled bottom portion(e.g., triangular) formed by the optically transmissive side walls 57A,57B. Each of the plates 190A, 190B has a correspondingly shaped bottomportion. The bottom portion of the first plate 190A has a first bottomedge 250A and a second bottom edge 250B. Similarly, the bottom portionof the second plate 1903 has a first bottom edge 252A and a secondbottom edge 252B. The first and second bottom edges of each plate arepreferably angularly offset from each other by the same angle that theside walls 57A, 57B are offset from each other (e.g., 90°).Additionally, the plates 190A, 190B are preferably positioned to receivethe chamber of the vessel between them such that the first side wall 57Ais positioned substantially adjacent and parallel to each of the firstbottom edges 250A, 252A and such that the second side wall 57B ispositioned substantially adjacent and parallel to each of the secondbottom edges 250B, 252B. This arrangement provides for easy opticalaccess to the optically transmissive side walls 57A, 57B and hence tothe chamber of the vessel. A gel or fluid may optionally be used toestablish or improve optical communication between each optics assemblyand the side walls 57A, 57B. The gel or fluid should have a refractiveindex close to the refractive indexes of the elements that it iscoupling.

Referring again to FIG. 28, the optics assemblies 216, 218 arepreferably arranged to provide a 90° angle between excitation anddetection paths. The 90° angle between excitation and detection pathsassures that a minimum amount of excitation radiation entering throughthe first side wall of the chamber exits through the second side wall.Also, the 90° angle permits a maximum amount of emitted radiation to becollected through the second side wall. In the preferred embodiment, thevessel 40 includes a locating tab 58 (see FIG. 22) that fits into a slotformed between the optics assemblies 216, 218 to ensure properpositioning of the vessel 40 for optical detection. For improveddetection, the module 147 also preferably includes a light-tight lid(not shown) that is placed over the top of the vessel 40 and madelight-tight to the housing 208 after the vessel is inserted between theplates 190.

Although it is presently preferred to locate the optics assemblies 216,218 next to the bottom edges of the plates 190, many other arrangementsare possible. For example, optical communication may be establishedbetween the optics assemblies 216, 218 and the walls of the vessel 40via optical fibers, light pipes, wave guides, or similar devices. Oneadvantage of these devices is that they eliminate the need to locate theoptics assemblies 216, 218 physically adjacent to the plates 190. Thisleaves more room around the plates in which to circulate cooling air orrefrigerant, so that cooling may be improved.

The heat-exchanging module 147 also includes a PC board 226 for holdingthe electronic components of the module and an edge connector 224 forconnecting the module 147 to the instrument 140 (FIG. 10). The heatingelements and temperature sensors on the plates 190, as well as theoptical boards 220, 222, are connected to the PC board 226 by flexcables (not shown in FIG. 28 for clarity of illustration). The module147 may also include a grounding trace 228 for shielding the opticaldetection circuit. The module 147 may optionally include an indicator,such as an LED 214, for indicating to a user the current status of themodule such as “heating,” “cooling,” “finished,” or “fault”.

The housing 208 may be molded from a rigid, high-performance plastic, orother conventional material. The primary functions of the housing 208are to provide a frame for holding the plates 190, optics assemblies216, 2.18, fan 212, and PC board 226. The housing 208 also preferablyprovides flow channels and ports for directing cooling air from the fan212 across the surfaces of the plates 190 and out of the housing. In thepreferred embodiment, the housing 208 comprises complementary pieces(only one piece shown in the schematic side view of FIG. 28) that fittogether to enclose the components of the module 147 between them.

Referring again to FIG. 23, the plates 190A, 190B may be made of variousthermally conductive materials including ceramics or metals. Suitableceramic materials include aluminum nitride, aluminum oxide, berylliumoxide, and silicon nitride. Other materials from which the plates may bemade include, e.g., gallium arsenide, silicon, silicon nitride, silicondioxide, quartz, glass, diamond, polyacrylics, polyamides,polycarbonates, polyesters, polyimides, vinyl polymers, and halogenatedvinyl polymers, such as polytetrafluoroethylenes. Other possible platematerials include chrome/aluminum, superalloys, zircaloy, aluminum,steel, gold, silver, copper, tungsten, molybdenum, tantalum, brass,sapphire, or any of the other numerous ceramic, metal, or polymericmaterials available in the art.

Ceramic plates are presently preferred because their inside surfaces maybe conveniently machined to very high smoothness for high wearresistance, high chemical resistance, and good thermal contact to theflexible walls of the reaction vessel. Ceramic plates can also be madevery thin, preferably between about 0.6 and 1.3 mm, for low thermal massto provide for extremely rapid temperature changes. A plate made fromceramic is also both a good thermal conductor and an electricalinsulator, so that the temperature of the plate may be well controlledusing a resistive heating element coupled to the plate.

Various thermal elements may be employed to heat and/or cool the plates190A, 190B and thus control the temperature of the reaction mixture inthe chamber 42. In general, suitable heating elements for heating theplate include conductive heaters, convection heaters, or radiationheaters. Examples of conductive heaters include resistive or inductiveheating elements coupled to the plates, e.g., resistors orthermoelectric devices. Suitable convection heaters include forced airheaters or fluid heat-exchangers for flowing fluids past the plates.Suitable radiation heaters include infrared or microwave heaters.Similarly, various cooling elements may be used to cool the plates. Forexample, various convection cooling elements may be employed such as afan, peltier device, refrigeration device, or jet nozzle for flowingcooling fluids past the surfaces of the plates. Alternatively, variousconductive cooling elements may be used, such as a heat sink, e.g. acooled metal block, in direct contact with the plates.

Referring to FIG. 24, each plate 190 preferably has a resistive heatingelement 206 disposed on its outer surface. The resistive heating element206 is preferably a thick or thin film and may be directly screenprinted onto each plate 190, particularly plates comprising a ceramicmaterial, such as aluminum nitride or aluminum oxide. Screen-printingprovides high reliability and low cross-section for efficient transferof heat into the reaction chamber. Thick or thin film resistors ofvarying geometric patterns may be deposited on the outer surfaces of theplates to provide more uniform heating, for example by having denserresistors at the extremities and thinner resistors in the middle.Although it is presently preferred to deposit a heating element on theouter surface of each plate, a heating element may alternatively bebaked inside of each plate, particularly if the plates are ceramic. Theheating element 206 may comprise metals, tungsten, polysilicon, or othermaterials that heat when a voltage difference is applied across thematerial. The heating element 206 has two ends which are connected torespective contacts 204 which are in turn connected to a voltage source(not shown in FIG. 24) to cause a current to flow through the heatingelement. Each plate 190 also preferably includes a temperature sensor192, such as a thermocouple, thermistor, or RTD, which is connected bytwo traces 202 to respective ones of the contacts 204. The temperaturesensor 192 is be used to monitor the temperature of the plate 190 in acontrolled feedback loop.

The plates have a low thermal mass to enable rapid heating and coolingof the plates. In particular, it is presently preferred that each of theplates has a thermal mass less than about 5 J/° C., more preferably lessthan 3 J/° C., and most preferably less than 1 J/° C. As used herein,the term thermal mass of a plate is defined as the specific heat of theplate multiplied by the mass of the plate. In addition, each plateshould be large enough to cover a respective major wall of the reactionchamber. In the presently preferred embodiment, for example, each of theplates has a width X in the range of 2 to 22 mm, a length Y in the rangeof 2 to 22 mm, and a thickness in the range of 0.5 to 5 mm. The width Xand length Y of each plate is selected to be slightly larger than thewidth and length of the reaction chamber. Moreover, each platepreferably has an angled bottom portion matching the geometry of thebottom portion of the reaction chamber, as previously described withreference to FIG. 34. Also in the preferred embodiment, each of theplates is made of aluminum nitride having a specific heat of about 0.75J/g° C. The mass of each plate is preferably in the range of 0.005 to5.0 g so that each plate has a thermal mass in the range of 0.00375 to3.75 J/° C.

The opposing plates 190 are positioned to receive the chamber of thevessel 40 between them such that the flexible major walls of thechaamber contact and conform to the inner surfaces of the plates. It ispresently preferred that the plates 190 be held in an opposingrelationship to each other using, e.g., brackets, supports, orretainers. Alternatively, the plates 190 may be spring-biased towardseach other as described in International Publication Number WO 98/38487,the disclosure of which is incorporated by reference herein. In anotherembodiment of the invention, one of the plates is held in a fixedposition, and the second plate is spring-biased towards the first plate.If one or more springs are used to bias the plates towards each other,the springs should be sufficiently stiff to ensure that the plates arepressed against the flexible walls of the vessel with sufficient forceto cause the walls to conform to the inner surfaces of the plates.

FIGS. 29-30 illustrate a preferred support structure 209 for holding theplates 190A, 190B in an opposing relationship to each other. FIG. 29shows an exploded view of the structure, and FIG. 30 shows an assembledview of the structure. For clarity of illustration, the supportstructure 209 and plates 190A, 190B are shown upside down relative totheir normal orientation in the heat-exchanging module of FIG. 28.Referring to FIG. 29, the support structure 209 includes a mountingplate 210 having the slot 148 formed therein. The slot 148 issufficiently large to enable the chamber of the vessel to be insertedthrough it. Spacing posts 230A, 230B extend from the mounting plate 210on opposite sides of the slot 148. Spacing post 230A has indentations232 formed on opposite sides thereof (only one side visible in theisometric view of FIG. 29), and spacing post 230B has indentations 234formed on opposite sides thereof (only one side visible in the isometricview of FIG. 29). The indentations 232, 234 in the spacing posts are forreceiving the edges of the plates 190A, 190B. To assemble the structure,the plates 190A, 190B are placed against opposite sides of the spacingposts 230A, 230B such that the edges of the plates are positioned in theindentations 232, 234. The edges of the plates are then held in theindentations using a suitable retention means. In the preferredembodiment, the plates are retained by retention clips 236A, 236B.Alternatively, the plates 190A, 190B may be retained by adhesive bonds,screws, bolts, clamps, or any other suitable means.

The mounting plate 210 and spacing posts 230A, 230B are preferablyintegrally formed as a single molded piece of plastic. The plasticshould be a high temperature plastic, such as polyetherimide, which willnot deform of melt when the plates 190A, 190B are heated. The retentionclips 230A, 230B are preferably stainless steel. The mounting plate. 210may optionally include indentations 240A, 240B for receiving flex cables238A, 238B, respectively, that connect the heating elements andtemperature sensors disposed on the plates 190A, 190B to the PC board226 of the heat-exchanging module 147 (FIG. 28). The portion of the flexcables 238A adjacent the plate 190A is held in the indentation 240A by apiece of tape 242A, and the portion of the flex cables 238B adjacent theplate 190B is held in the indentation 240B by a piece of tape 242B.

FIG. 31 is an isometric view of the assembled support structure 209. Themounting plate 210 preferably includes tabs 246 extending from oppositesides thereof for securing the structure 209 to the housing of theheat-exchanging module. Referring again to FIG. 28, the housing 208preferably includes slots for receiving the tabs to hold the mountingplate 210 securely in place. Alternatively, the mounting plate 210 maybe attached to the housing 208 using, e.g., adhesive bonding, screws,bolts, clamps, or any other conventional means of attachment.

Referring again to FIG. 29, the support structure 209 preferably holdsthe plates 190A, 190B so that their inner surfaces are angled veryslightly towards each other. In the preferred embodiment, each of thespacing posts 230A, 230B has a wall 244 that is slightly tapered so thatwhen the plates 190A, 190B are pressed against opposite sides of thewall, the inner surfaces of the plates are angled slightly towards eachother. As best shown in FIG. 23, the inner surfaces of the plates 190A,190B angle towards each other to form a slightly V-shaped slot intowhich the chamber 42 is inserted. The amount by which the inner surfacesare angled towards each other is very slight, preferably about 1° fromparallel. The surfaces are angled towards each other so that, prior tothe insertion of the chamber 42 between the plates 190A, 190B, thebottoms of the plates are slightly closer to each other than the tops.This slight angling of the inner surfaces enables the chamber 42 of thevessel to be inserted between the plates and withdrawn from the platesmore easily. Alternatively, the inner surfaces of the plates 190A, 190Bcould be held parallel to each other, but insertion and removal of thevessel 40 would be more difficult.

In addition, the inner surfaces of the plates 190A, 190B are preferablyspaced from each other a distance equal to the thickness of the frame46. In embodiments in which the inner surfaces are angled towards eachother, the centers of the inner surfaces are preferably spaced adistance equal to the thickness of the frame 46 and the bottoms of theplates are initially spaced a distance that is slightly less than thethickness of the frame 46. When the chamber 42 is inserted between theplates 190A, 190B, the rigid frame 46 forces the bottom portions of theplates apart so that the chamber 42 is firmly sandwiched between theplates. The distance that the plates 190A, 190B are wedged apart by theframe 46 is usually very small, e.g., about 0.035 mm if the thickness ofthe frame is 1 mm and the inner surfaces are angled towards each otherby 1°.

Referring again to FIG. 30, the retention clips 236A, 236B should besufficiently flexible to accommodate this slight outward movement of theplates 190A, 190B, yet sufficiently stiff to hold the plates within therecesses in the spacing posts 230A, 230B during insertion and removal ofthe vessel. The wedging of the vessel between the plates 190A, 190Bprovides an initial preload against the chamber and ensures that theflexible major walls of the chamber, when pressurized, establish goodthermal contact with the inner surfaces of the plates.

Referring again to FIG. 28, to limit the amount that the plates 190 canspread apart due to the pressurization of the vessel 40, stops may bemolded into the housings of optics assemblies 216, 218. As shown in FIG.32, the housing 249 of the optics assembly 218 includes claw-like stops247A, 247B that extend outwardly from the housing. As shown in FIG. 33,the housing 249 is positioned such that the bottom edges of the plates190A, 190B are inserted between the stops 247A, 247B. The stops 247A,247B thus prevent the plates 190A, 190B from spreading farther than apredetermined maximum distance from each other. Although not shown inFIG. 33 for illustrative clarity, the optics assembly 216 (see FIG. 28)has a housing with corresponding stops for preventing the other halvesof the plates from spreading farther than the predetermined maximumdistance from each other. Referring again to FIG. 23, the maximumdistance that stops permit the inner surfaces of the plates 190A, 190Bto be spaced from each other should closely match the thickness of theframe 46. Preferably, the maximum spacing of the inner surfaces of theplates 190A, 190B is slightly larger than the thickness of the frame 46to accommodate tolerance variations in the vessel 40 and plates 190A,190B. For example, the maximum spacing is preferably about 0.1 to 0.3 mmgreater than the thickness of the frame 46.

FIG. 35 is a schematic, block diagram of the electronic components ofthe heat-exchanging module 147. The module includes a connector 224 orflex cable for connection to the main logic board of the instrument. Themodule also includes heater plates 190A, 190B each having a resistiveheating element as described above. The plates 190A, 190B are wired inparallel to receive power input 253 from the instrument. The plates190A, 190B also include temperature sensors 192A, 192B that outputanalog temperature signals to an analog-to-digital converter 264. Theconverter 264 converts the analog signals to digital signals and routesthem to the microcontroller in the instrument through the connector 224.

The heat-exchanging module also includes a cooling system, such as a fan212, for cooling the plates 190A, 190B and the reaction mixturecontained in the vessel inserted between the plates. The fan 212 isactivated by switching a power switch 272, which is in turn controlledby a control logic block 270 that receives control signals from themicrocontroller. The module further includes four light sources, such asLEDs 200, for excitation of labeled analytes in the reaction mixture andfour detectors 198, preferably photodiodes, for detecting fluorescentemissions from the reaction mixture. The module also includes anadjustable current source 255 for supplying a variable amount of current(e.g., in the range of 0 to 30 mA) to each LED to vary the brightness ofthe LED. A digital-to-analog converter 260 is connected between theadjustable current source 255 and the microcontroller to permit themicrocontroller to adjust the current source digitally.

The adjustable current source 255 is preferably used to ensure that eachLED has about the same brightness when activated. Due to manufacturingvariances, many LEDs have different brightnesses when provided with thesame amount of current. Therefore, it is presently preferred to test thebrightness of each LED during manufacture of the heat-exchanging moduleand to store calibration data in a memory 268 of the module. Thecalibration data indicates the correct amount of current to provide toeach LED. The microcontroller reads the calibration data from the memory268 and controls the current source 255 accordingly.

The module additionally includes a signal conditioning/gainselect/offset adjust block 262 comprised of amplifiers, switches,electronic filters, and a digital-to-analog converter. The block 262adjusts the signals from the detectors 198-to increase gain, offset, andreduce noise. The microcontroller controls block 262 through a digitaloutput register 266. The output register 266 receives data from themicrocontroller and outputs control voltages to the block 262. The block262 outputs the adjusted detector signals to the microcontroller throughthe analog-to-digital converter 264 and the connector 224. The modulealso includes the memory 268, preferably a serial EEPROM, for storingdata specific to the module, such as calibration data for the LEDs 200,thermal plates 190A, 190B, and temperature sensors 192A, 192B.

The operation of the cartridge and instrument will now be described. Asshown in FIG. 3, a fluid sample to be analyzed is added to the samplechamber 65 through the sample port 64 and the cap 30 screwed into theport 64 to seal the port shut. Referring to FIG. 10, the cartridge 20 isthen placed into the cartridge nest 141 of the instrument 140 forprocessing. All valves in the cartridge 20 are initially closed when thecartridge is placed into the instrument 140. When the cartridge isplaced in the instrument, the transducer 92 contacts an external surfaceof the flexible gasket 63 forming the bottom wall of the lysing chamber86, as shown in FIG. 5.

Referring again to FIG. 10, the instrument 140 is preferablycomputer-controlled to perform the functions described in the followingsection, e.g., opening and closing valves in the cartridge using valveactuators 142, providing pressure to the cartridge through nozzles 145,activating the transducer 92, sensing liquid presence or liquid levelsusing optical sensors 143 and 144, and controlling the heat-exchangingand optical detection module 147. A programmer having ordinary skill inthe art will be able to program a microcontroller and/or computer toperform these functions based upon the following description.

Referring to FIG. 9, liquids are preferably forced to flow through thecartridge using differential pressure. Although positive pressure isdescribed herein, negative pressure (vacuum) may also be used to controlfluid flow in the cartridge. The maximum amount of positive pressurethat can be applied is usually limited by the hydrophobic membraneswhich may reach liquid break-through pressure above 30 pounds per squareinch (psi). The lower limit of pressure is limited by the need to movesample and other fluids through the cartridge sufficiently quickly tomeet assay goals. Below 1 psi, for example, sample may not flowefficiently through the filter stack 87. Pressure in the range of 6 to20 psi is generally adequate. The sample flow rate through the cartridgeis preferably in the range of 10 to 30 ml/minute. The wash flow rate maybe slower, e.g. 6 to 18 ml/minute so that the wash effectively washesthe lysing chamber 86.

A specific protocol will now be described with reference to FIG. 9 toillustrate the operation of the cartridge. It is be understood that thisis merely an example of one possible protocol and is not intended tolimit the scope of the invention. To begin, the cartridge is preferably63 primed with wash solution from the wash chamber 66 before the fluidsample is forced to flow from the sample chamber 65. To prime thecartridge, valves 111 and 115 are opened and a pressure of 10 psi isapplied to the chamber 66 through the pressure port 116 for about twoseconds. A small portion of the wash solution flows through the channels117 and 106, through the lysing chamber 86, through the channels 109 and110, into the U-shaped channel 122, and all the way to the hydrophobicmembrane below the pressure port 128.

Following priming, valve 115 and pressure port 116 are closed and valves107 and 114 are opened. At the same time, a pressure of 20 psi isapplied to the sample chamber 65 through the pressure port 105 for about15 seconds to force the sample to flow through the channel 106, throughthe filter stack 87 in the chamber 86, through the channels 110, 111,112 and into the vented waste chamber 68. As the sample passes thedetection region 136 in the channel 106, the reflective optical sensor144 (FIG. 13) may be used to determine when the sample chamber 65 hasbeen emptied. As the sample liquid flows through the filter stack 87,target cells or viruses in the sample are captured. When a predeterminedvolume of sample reaches the waste chamber 68, some of the liquid spillsover into the sensor chamber 120, triggering the next step in theprotocol. Alternatively, instead of using feedback from optical sensorsto trigger events, the steps in a predetermined protocol may simply betimed, e.g., applying predetermined pressures for predetermineddurations of time to move known volumes of fluid at known flow rates.

The flow-through design of the lysing chamber 86 permits target cells orviruses from a relatively large sample volume to be concentrated into amuch smaller volume for amplification and detection. This is importantfor the detection of low concentration analyte in the sample, such asnucleic acid. In particular, the ratio of the volume of the sampleforced to flow through the lysing chamber 86 to the volume capacity ofthe chamber 86 is preferably at least 2:1, and more preferably at least5:1. The volume of sample forced to flow through the chamber 86 ispreferably at least 100 μl, and more preferably at least 1 ml. In thepresently preferred embodiment, a sample volume of 5 ml is forced toflow through the lysing chamber 86, and the chamber 86 has a volumecapacity of about 0.5 ml, so that the ratio is 10:1. In addition, thelysing chamber 86 may be sonicated (e.g.,using an ultrasonic horncoupled to a wall of the chamber) as the sample is forced to flowthrough the chamber. Sonicating the chamber 86 helps to prevent cloggingof the filter stack 87, providing for more uniform flow through thechamber 86. In particular, the sound waves help keep particulate matteror the beads in the filter stack from clogging one or more filters.

In the next step, valves 111, 114, 115 are opened and a pressure of 20psi is applied to the wash chamber 66 for about seven seconds to forcethe wash solution to flow through the channels 117 and 106 into thelysing chamber 86. The washing solution washes away PCR inhibitors andcontaminants from the lysing chamber 86 and carries then through thechannels 109, 110, and 112 into the waste chamber 68. A variety ofsuitable wash solutions of varying pH, solvent composition, and ionicstrength may be used for this purpose and are well known in the art. Forexample, a suitable washing reagent is a solution of 80 mM potassiumacetate, 8.3 mM Tris-HCl, pH 7.5, 40 uM EDTA, and 55% ethanol. Thelysing chamber 86 may be sonicated (e.g., using an ultrasonic horncoupled to a wall of the chamber) while the wash solution is forced toflow through the chamber. Sonicating the chamber 86 helps to preventclogging of the filter stack 87, providing for more uniform flow throughthe chamber 86 as previously described. In addition, the sound waves mayhelp loosen the material to be washed away. When the incremental volumeof wash solution reaches the waste chamber 68, some of the liquid spillsover into the sensor chamber 121, triggering the next step in theprotocol.

In the next step, valve 115 is closed and valve 119 is opened while apressure of 15 psi is applied to the reagent chamber 67 through thepressure port 118 for about three seconds. The pressure forces lysingreagent to flow from the chamber 67 through the channels 117, 106 intothe lysing chamber 86, and into the channel 110. The chamber 86 is thusfilled with liquid. Suitable lysing reagents include, e.g., solutionscontaining a chaotropic salt, such as guanidine HCl, guanidinethiocyanate, guanidine isothiocyanate, sodium iodide, urea, sodiumperchlorate, and potassium bromide. In the presently preferredembodiment, a lysing reagent that is not inhibitory to PCR is used. Thelysing reagent comprises 10 mM tris, 5% tween-20, 1 mM tris(2-carboxyethyl phosphine hydrochloride), 0.1 mM Ethylene Glycol-bis(b-amino-ethyl ether)-N,N,N′, N′- etracetic acid. After the lysingchamber 86 is filled with lysing reagent, the valves 111, 114 areclosed. Valve 119 remains open and a pressure of 20 psi is applied topressure port 118. The static pressure in the lysis chamber 86 istherefore increased to 20 psi in preparation for the lysis of the cellsor viruses trapped in the filter stack 87.

Referring again to FIG. 5, the pressurization of the lysing chamber 86is important because it ensures effective coupling between thetransducer 92 and the flexible wall 63 of the lysing chamber 86. Todisrupt the cells or viruses in the chamber 86, the transducer 92 isactivated (i.e., set into vibratory motion). The flexible wall 63 of thelysing chamber 86 transfers the vibratory motion of the transducer 92 tothe liquid in the chamber 86 by allowing slight deflections withoutcreating high stresses in the wall. The wall 63 may be formed by theelastomeric membrane as previously described. Alternatively, the wallmay be a film or sheet of polymeric material (e.g., a polypropylenefilm) preferably having a thickness in the range of 0.025 to 0.1 mm. Thetransducer 92 is preferably an ultrasonic horn for sonicating thechamber 86. The chamber 86 is preferably sonicated for 10 to 40 secondsat a frequency in the range of 20 to 60 kHz. In the exemplary protocol,the chamber is sonicated for 15 seconds at a frequency of 47 kHz. Theamplitude of the horn tip is preferably in the range of 20 to 25 μm(measured peak to peak).

As the tip of the transducer 92 vibrates, it repeatedly impacts theflexible wall 63. On its forward stroke (in the upward direction in FIG.6), the tip of the transducer 92 pushes the wall 63 and creates apressure pulse or pressure wave in the chamber 86. On its retreatingstroke (downward in FIG. 5), the tip of the transducer 92 usuallyseparates from the flexible wall 63 because the flexible wall 63 cannotmove at the same frequency as the transducer. On its next forwardstroke, the tip of the transducer 92 once again impacts the wall 63 in ahead-on collision as the tip and wall speed towards each other. Becausethe transducer 92 and the wall 63 separate as the transducer 92vibrates, the effective forward stroke of the transducer is less thanits peak-to-peak amplitude. The effective forward stroke determines thelevel of sonication in the chamber 86. It is therefore important toincrease the static pressure in the lysing chamber 86 so that when thetip of the transducer 92 retreats, the flexible wall 63 is forcedoutwardly to meet the tip on its return stroke. The static pressure inthe chamber 86 should be sufficient to ensure that the effective forwardstroke of the transducer 92 generates pressure pulses or pressure wavesin the chamber 86. It is presently preferred to increase the staticpressure in the chamber 86 to at least 5 psi above the ambient pressureexternal to the cartridge, and more preferably to a pressure in therange of 15 to 25 psi above the ambient pressure.

On each forward stroke, the transducer 92 imparts a velocity to theliquid in the chamber 86, thus creating a pressure wave that quicklysweeps across the chamber 86. The bead in the filter stack 87 (FIG. 6)are agitated by the pressure waves in the chamber 86. The pressure wavespropel the beads into violent motion in the chamber 86, and the beadsmechanically rupture the cells or viruses to release the material (e.g.,nucleic acid) therefrom. It should be noted that some types of cells,such as blood cells, are relatively weak and may be disrupted using onlypressure waves (e.g., ultrasonic waves) without the use of beads. Othertypes of cells (particularly spores) have highly resistant cell wallsand beads are generally required for effective lysis.

Referring again to FIG. 9, following disruption of the cells or viruses,valves 111, 124 are opened and a pressure of 12 psi is delivered forabout 4 seconds to the reagent chamber 67 through the pressure port 118.The pressure forces the lysis reagent to elute the nucleic acid from thefilter stack 87 and to flow with the nucleic acid into theneutralization chamber 70. The lysing chamber 86 may be sonicated (e.g.,using an ultrasonic horn coupled to a wall of the chamber) while theeluting the nucleic acid. Sonicating the chamber 86 may help preventclogging of the filter stack 87, as previously described. The chamber420 is partially filled (e.g., half-filled) with neutralizer, such asdetergent, for neutralizing the lysing reagent. If a lysing reagentnon-inhibitory to PCR is used, the neutralizer is optional.

In the next step, the valve 124 is closed to hold the lysing reagent,analyte, and neutralizer in the chamber 70. The valve 114 is opened anda pressure of 15 psi is applied for about three seconds through thepressure port 128 to force any liquid in the U-shaped channel 122 toflow into the waste chamber 68. Next, valves 124 and 126 are opened anda pressure of 15 psi is applied for about five seconds through thepressure port 123 on top of the neutralizer chamber 70. The pressureforces the neutralized lysing reagent and nucleic acid in the chamber 70to flow into the channel 122 and into the master mix chamber 71. Thevalve 126 to the master mix chamber 71 is then closed. The master mixchamber contains PCR reagents and fluorescent probes that mix with theneutralized lysing reagent and nucleic acid to form a reaction mixture.

In the next step, the channel 122 is cleared by opening valve 114 towaste chamber 68 and applying a pressure of 15 psi for about one secondto pressure port 128. In the next step, the reaction mixture formed inthe master mix chamber 71 is moved into the reaction vessel 40 asfollows. Valves 126, 127, and 133 are opened and a pressure of 15 psi isapplied for about six seconds to the pressure port 125 on top of themaster mix chamber 71 to force the reaction mixture to flow through thechannel 122, valve 127, and channel 80 into the reaction vessel 40through the port 41. The reaction mixture fills the chamber 42 of thevessel, displacing air in the chamber which exits through the outletchannel 52. The air escaping through the outlet channel 52 travels inchannel 81 past sensor region 130 and into channel 131. From channel131, the air flows into channel 132, through valve 133, channel 134, andexits the cartridge through the vent 36. When a volume of reactionmixture sufficient to fill the chamber 42 has flowed into the vessel,excess reaction mixture exits the vessel through the outlet channel 52.The excess reaction mixture flows into channel 81 and is opticallydetected in the sensor region 130. When the reaction mixture isdetected, valve 133 is closed while pressure from the pressure port 125is applied to pressurize the reaction chamber 42.

Referring again to FIG. 23, the pressurization of the chamber 42 expandsthe flexible major walls 48 of the vessel. In particular the pressureforces the major walls 48 to contact and conform to the inner surfacesof the plates 190A, 190B. This ensures optimal thermal conductancebetween the plates 190A, 190B and the reaction mixture in the chamber42. It is presently preferred to pressurize the chamber 42 to a pressurein the range of 2 to 30 psi above ambient pressure. This range ispresently preferred because 2 psi is generally enough pressure to ensureconformity between the walls 48 and the surfaces of the plates 190A,190B, while pressures above 30 psi may cause bursting of the walls 48,deformation of the frame 46 or plates 190A, 190B, or bursting of thehydrophobic membranes in the cartridge. More preferably, the chamber 42is pressurized to a pressure in the range of 8 to 15 psi above ambientpressure. This range is more preferred because it is safely within thepractical limits described above. When the chamber 42 is pressurized,the reaction mixture in the vessel 40 is thermally processed andoptically interrogated to determine the presence or absence of a targetanalyte in the mixture.

Referring again to FIG. 35, the reaction mixture is thermally processedbetween the plates 190A, 190B using standardproportional-integral-derivative (PID) control using target temperaturesand feedback signals from the temperature sensors 92A, 192B.Proportioning may be accomplished either by varying the ratio of “on”time to “off” time, or, preferably with proportional analog outputswhich decrease the average power being supplied either to the heatingelements on the plates 190A, 190B or to the fan 212 as the actualtemperature of the plates 190A, 190B approaches the desired set pointtemperature. PID control combines the proportional mode with anautomatic reset function (integrating the deviation signal with respectto time) and rate action (summing the integral and deviation signal toshift the proportional band). Standard PID control is well known in theart and need not be described further herein. Alternatively, thereaction mixture may be thermally processed using a modified version ofPID control described in International Publication Number WO 99/48608(Application Number PCT/US99/06628) the disclosure of which isincorporated by reference herein.

As the reaction mixture is thermally cycled between the heater plates190A, 1908 to amplify one or more target nucleic acid sequences in themixture, the mixture is optically interrogated, preferably at the lowesttemperature point in each cycle. Optical interrogation is accomplishedby sequentially activating each of the LEDs 200 to excite differentfluorescently-labeled analytes in the mixture and by detecting lightemitted (fluorescent output) from the chamber 42 using detectors the198. Referring again to FIG. 22, excitation beams are preferablytransmitted to the chamber 42 through the optically transmissive sidewall 57A, while fluorescent emission is detected through the side wall57B.

One advantage of the cartridge of the present invention is that itallows the intracellular material from a relatively large volume offluid sample, e.g. several milliliters or more, to be separated from thesample and concentrated into a much smaller volume of reaction fluid,e.g., 100 μL or less. The cartridge permits extraordinary concentrationfactors by efficiently extracting material from milliliter quantities offluid sample. In particular, the sample chamber 65 preferably has avolume capacity in the range of 100 μl to 12 ml. More preferably, thesample chamber 65 has a volume capacity of at least 1 ml. The lowerlimit of 1 ml is preferred because at least 1 ml of sample should beanalyzed to detect low concentration analytes such as nucleic acid. Theupper limit of 12 ml is preferred because a sample volume greater than12 ml would require a much larger cartridge and likely clog the filterstack. In the presently preferred embodiment, the sample chamber has avolume capacity of 5.5 ml for holding 5 ml of sample.

The wash chamber 66 has a volume capacity proportional to the volume ofthe lysing chamber 86. In particular, the wash chamber 66 preferablyholds a volume of wash that is at least one to two times the volume ofthe lysing chamber 86 to ensure that there is enough wash solution towash out PCR inhibitors and debris from the chamber 86. In the presentlypreferred embodiment, the volume of the lysing chamber 86 is about 0.5ml and the volume of the wash chamber 66 is 2.5 ml for holding 2 ml ofwash solution. The lysing chamber volume of 0.5 ml is a compromisebetween a size large enough to avoid clogging of the filter stack 87 anda size small enough to concentrate analyte into a small volume forimproved amplification and detection.

The reagent chamber 67 preferably holds a volume of lysing reagent thatis at least one to two times the volume of the lysing chamber 86 so thatthere is sufficient lysing reagent to pressurize the chamber and toelute nucleic acid from the chamber. In the presently preferredembodiment, the chamber 67 has a volume capacity of 1.5 ml for holdingabout 1 to 1.5 ml of lysing reagent. The waste chamber 68 has a volumecapacity sufficient to hold the sample, wash solution, and unused lysingreagent. The waste chamber 68 is sized at 9.5 ml volume capacity in thepreferred embodiment.

The size of the neutralization chamber 70 is dependent upon the volumeof the lysing chamber 86 since the neutralizer in the chamber 70neutralizes the volume of lysing reagent that fills the lysing chamber86. It is currently preferred that the lysing chamber have a volume if0.5 ml, so the chamber 70 has a volume capacity of 1.0 ml for holdingabout 0.5 ml of neutralizer that is mixed with 0.5 ml of the lysingreagent and eluted analyte. The volume capacity of the master mixchamber 71 should be sufficient to produce a reaction mixture to fillthe vessel 40 and the channels 122, 127 leading to the vessel. In thepresently preferred embodiment, the master mix chamber has a volumecapacity of 200 μl for holding an initial load of 100 μl of master mixto which is added 100 μl of neutralized lysing reagent and elutedanalyte to form the reaction mixture.

The flow channels in the cartridge are generally D-shaped of thechannel) and preferably have a width or diameter in the range of{fraction (1/64)} to ⅛ of an inch (0.4 to 3.2 mm), and more preferably awidth of {fraction (1/32)} to {fraction (1/16)} of an inch (0.8 to 1.6mm). These ranges are presently preferred to avoid having channels tonarrow (which creates flow restriction) and to avoid having channels toowide (which yields unused volumes of liquid sitting in the flow path).

Many modifications to the structure and operation of the cartridge andinstrument are possible in alternative embodiments. For example,although amplification by PCR is presently preferred, the cartridge andinstrument may be used to amplify nucleic acid sequences using anyamplification method, including both thermal cycling amplificationmethods and isothermal amplification methods. Suitable thermal cyclingmethods include, but are not limited to, the Polymerase Chain Reaction(PCR; U.S. Pat. Nos. 4,683,202, 4,683,195 and 4,965,188); ReverseTranscriptase PCR (RT-PCR); DNA Ligase Chain Reaction (LCR;International Patent Application No. WO 89/09835); andtranscription-based amplification (D. Y. Kwoh et al. 1989, Proc. Natl.Acad. Sci. USA 86, 1173-1177). Suitable isothermal amplification methodsuseful in the practice of the present invention include, but are notlimited to, Rolling Circle Amplification; Strand DisplacementAmplification (SDA; Walker et al. 1992, Proc. Nati. Acad. Sci. USA 89,392-396); Q-.beta. replicase (Lizardi et al. 1988, Bio/Technology 6,1197-1202); Nucleic Acid-Based Sequence Amplification (NASBA; R.Sooknanan and L. Malek 1995, Bio/Technology 13, 563-65); andSelf-Sustained Sequence Replication (3SR; Guatelli et al. 1990, Proc.Nati. Acad. Sci. USA 87, 1874-1878).

Moreover, the cartridge and instrument may be used to conduct chemicalreactions other than nucleic acid amplification. Further, althoughfluorescence excitation and emission detection is preferred, opticaldetection methods such as those used in direct absorption and/ortransmission with on-axis geometries may also be used to detect analytein the cartridge. Another possible detection method is time decayfluorescence. Additionally, the cartridge is not limited to detectionbased upon fluorescent labels. For example, detection may be based uponphosphorescent labels, chemiluminescent labels, orelectrochemiluminescent labels.

A fluid sample may be introduced into the cartridge by a variety ofmeans, manual or automated. For manual addition, a measured volume ofmaterial may be placed into a receiving area of the cartridge through aninput port and a cap is then placed over the port. Alternatively, agreater amount of sample material than required for the analysis can beadded to the cartridge and mechanisms within the cartridge can effectthe precise measuring and aliquoting of the sample needed for thespecified protocol. It may be desirable to place certain samples, suchas tissue biopsy material, soil, feces, exudates, and other complexmaterial into another device or accessory and then place the secondarydevice or accessory into the cartridge. For example, a piece of tissuemay be placed into the lumen of a secondary device that serves as thecap to the input port of the cartridge. When the cap is pressed into theport the tissue is forced through a mesh that slices or otherwisedivides the tissue.

For automated sample introduction, additional design features of thecartridge are employed and, in many cases, impart specimen accessionfunctionality directly into the cartridge. With certain samples, such asthose presenting a risk of hazard to the operator or the environment,such as human retrovirus pathogens, the transfer of the sample to thecartridge may pose a risk. Thus, in one embodiment, a syringe may beintegrated into a device to provide a means for moving external fluidicsamples directly into the cartridge. Alternatively, a venous punctureneedle and an evacuated blood tube can be attached to the cartridgeforming an assembly that can be used to acquire a sample of blood. Aftercollection, the tube and needle are removed and discarded, and thecartridge is then placed in an instrument to effect processing. Theadvantage of such an approach is that the operator or the environment isnot exposed to pathogens.

The input port can be designed with a consideration of appropriate humanfactors as a function of the nature of the intended specimen. Forexample, respiratory specimens may be acquired from the lowerrespiratory tract as expectorants from coughing, or as swab or brushsamples from the back of the throat or the nares. In the former case,the input port can be designed to allow the patient to cough directlyinto the cartridge or to otherwise facilitate spitting of theexpectorated sample into the cartridge. For brush or swab specimens, thespecimen is placed into the input port where features of the port andclosure facilitate the breaking off and retaining of the end of the swabor brush in the cartridge receiving area.

In another embodiment, the cartridge includes input and output tubesthat may be positioned in a sample pool of very large volume, such as aflowing stream of water, so that the sample material flows through thecartridge. Alternatively, a hydrophilic wicking material can serve as aninteractive region so that the entire cartridge can be immersed directlyinto the specimen, and a sufficient amount of specimen is absorbed intothe wicking material. The cartridge is then removed, and can betransported to the laboratory or analyzed directly using a portableinstrument. In another embodiment, tubing can be utilized so that oneend of the tube is in direct communication with the cartridge to providea fluidic interface with at least one interactive region and the otherend is accessible to the external environment to serve as a receiver forsample.

The tube can then be placed into a specimen and serve as a sipper. Thecartridge itself may also serve as the actual specimen collectiondevice, thereby reducing handling and inconvenience. In the case ofspecimens involved in legal disputes or criminal investigations, thedirect accessing of the test material into the fluidic cartridge isadvantageous because the chain of custody is conveniently and reliablypreserved.

Referring again to FIG. 9, reagents may be exogenously introduced intothe cartridge before use, e.g., through sealable openings in the reagentchamber 67, neutralizer chamber 70, and master mix chamber 71.Alternatively, the reagents may be placed in the cartridge duringmanufacture, e.g., as aqueous solutions or dried reagents requiringreconstitution. The particular format is selected based on a variety ofparameters, including whether the interaction is solution-phase orsolid-phase, the inherent thermal stability of the reagent, speed ofreconstitution, and reaction kinetics. Reagents containing compoundsthat are thermally unstable when in solution can be stabilized by dryingusing techniques such as lyophilization. Additives, such as simplealcohol sugars, methylcelluloses, and bulking proteins may be added tothe reagent before drying to increase stability or reconstitutability.

Referring again to FIG. 21, the reaction vessel 40 does not require twoflexible sheets forming opposing major walls 48 of the reaction chamber42. For example, in one alternative embodiment, the vessel 40 has onlyone flexible sheet forming a major wall of the chamber. The rigid frame46 defines the other major wall of the chamber, as well as the sidewalls of the chamber. In this embodiment, the major wall formed by theframe 46 should have a minimum thickness of about 0.05 inches (1.25 mm)which is typically the practical minimum thickness for injectionmolding, while the flexible sheet may be as thin as 0.0005 inches(0.0125 mm). The advantage to this embodiment is that the manufacturingof the reaction vessel 40 is simplified, and hence less expensive, sinceonly one flexible sheet need be attached to the frame 46. Thedisadvantage is that the heating and cooling rates of the reactionmixture are likely to be slower since the major wall formed by the frame46 will probably not permit as high a rate of heat transfer as the thin,flexible sheet.

Referring to FIG. 28, the heat exchaging module 147 only requires onethermal surface for contacting a flexible wall of the reaction vessel 40and one thermal element for heating and/or cooling the thermal surface.The advantage to using one thermal surface and one thermal element isthat the apparatus may be manufactured less expensively. Thedisadvantage is that the heating and cooling rates are likely to beabout twice as slow. Further, although it is presently preferred thatthe thermal surfaces be formed by the thermally conductive plates 190,each thermal surface may be provided by any rigid structure having acontact area for contacting a wall of the vessel 40. The thermal surfacepreferably comprises a material having a high thermal conductivity, suchas ceramic or metal. Moreover, the thermal surface may comprise thesurface of the thermal element itself. For example, the thermal surfacemay be the surface of a thermoelectric device that contacts the wall toheat and/or cool the chamber.

It is presently preferred to build the transducer into the instrument140. In another embodiment, however, the transducer may be built intothe cartridge. For example, a piezoelectric disk may be built into thecartridge for sonicating the lysing chamber. Alternatively, a speaker orelectromagnetic coil device may be built into the cartridge. In theseembodiments, the cartridge includes suitable electrical connectors forconnecting the transducer to a power supply. In embodiments in which thetransducer is built into the cartridge, the transducer should beprevented from contacting the fluid sample directly, e.g., thetransducer should be laminated or separated from the sample by a chamberwall. Further, lysis of the cells or viruses may be performed using aheater in place of or in combination with a transducer. The heater maybe a resistive heating element that is part of cartridge, or the heatercould be built into the instrument that receives the cartridge. In thisembodiment, the cells or viruses are disrupted by heating the lysischamber to a high temperature (e.g., 95° C.) to disrupt the cell walls.

Although the above description contains many specificities, these shouldnot be construed as limitations on the scope of the invention, butmerely as examples of some of the presently preferred embodiments. Manymodifications or substitutions may be made to the apparatus and methodsdescribed without departing from the scope of the invention.

Therefore, the scope of the invention should be determined by thefollowing claims and their legal equivalents.

What is claimed is:
 1. A device for conducting a chemical reaction, thedevice comprising: a) a body having at least first and second channelsformed therein; and b) a reaction vessel extending from the body, thereaction vessel having: i) a rigid frame defining side walls of areaction chamber; ii) first and second polymeric films attached toopposite sides of the rigid frame to form opposing major walls of thereaction chamber; iii) an inlet port connected to the reaction chambervia an inlet channel; and iv) an outlet port connected to the reactionchamber via an outlet channel; wherein the inlet port of the vessel isconnected to the first channel in the body and wherein the outlet portof the vessel is connected to the second channel in the body.
 2. Thedevice of claim 1, wherein each of the major walls is sufficientlyflexible to conform to a respective thermal surface.
 3. The device ofclaim 1, wherein at least two of the side walls are opticallytransmissive and angularly offset from each other.
 4. The device ofclaim 1, wherein the ratio of the width of the reaction chamber to thethickness of the reaction chamber is at least 4:1, and wherein thereaction chamber has a thickness less than 2 mm.
 5. The device of claim1, wherein the body further includes a vent in fluid communication withthe second channel for venting gas from the second channel.
 6. Thedevice of claim 1, further comprising a differential pressure source forforcing fluid in the first channel in the body to flow through the inletport of the vessel and into the reaction chamber.
 7. The device of claim1, wherein the body further includes a mixing chamber for mixing nucleicacid with amplification reagents, the mixing chamber being connected tothe inlet port of the vessel via the first channel.
 8. The device ofclaim 1, wherein the body has formed therein: i) a sample flow path; andii) a separation region in the sample flow path for separating a desiredanalyte from a fluid sample, the separation region being connected tothe inlet port of the vessel via the first channel.
 9. The device ofclaim 8, wherein the separation region in the body comprises: a) alysing chamber in the sample flow path for lysing cells or viruses inthe sample to release material therefrom; and b) at least one solidsupport positioned in the lysing chamber for capturing the cells orviruses to be lysed.
 10. The device of claim 1, further comprising: a)at least first and second thermal surfaces for contacting the first andsecond films, respectively; b) means for increasing the pressure in thereaction chamber, wherein the pressure increase in the chamber issufficient to force the first and second films to conform to the firstand second surfaces, respectively; and c) at least one thermal elementfor heating or cooling the surfaces to induce a temperature changewithin the chamber.
 11. The device of claim 1, wherein at least two ofthe side walls are optically transmissive and angularly offset from eachother, and the device further comprises an optics system having at leastone light source for transmitting light to the reaction chamber througha first one of the optically transmissive side walls and having at leastone detector for detecting light emitted from the chamber through asecond one of the optically transmissive side walls.
 12. A device forconducting a chemical reaction, the device comprising: a) a body having:i) a sample flow path; and ii) a separation region in the sample flowpath for separating a desired analyte from a fluid sample; b) a reactionvessel extending from the body, the reaction vessel having: i) areaction chamber; ii) an inlet port connected to the reaction chambervia an inlet channel; and iii) an outlet port connected to the reactionchamber via an outlet channel; wherein the body further has at leastfirst and second channels formed therein, the separation region beingconnected to the inlet port of the vessel via the first channel in thebody, and the outlet port of the vessel being connected to the secondchannel in the body.
 13. The device of claim 12, wherein the separationregion comprises: a) a lysing chamber in the sample flow path for lysingcells or viruses in the sample to release material therefrom; and b) atleast one solid support positioned in the lysing chamber for capturingthe cells or viruses to be lysed.
 14. The device of claim 12, whereinthe vessel includes a plurality of walls defining the reaction chamber,at least one of the walls comprises a flexible sheet or film, and thedevice further comprises: a) at least one thermal surface for contactingthe sheet or film; b) means for increasing the pressure in the reactionchamber, wherein the pressure increase in the chamber is sufficient toforce the sheet or film to conform to the thermal surface; and c) atleast one thermal element for heating or cooling the surface to induce atemperature change in the reaction chamber.
 15. The device of claim 12,wherein the vessel includes two opposing major walls and sidewallsconnecting the major walls to each other to form the reaction chamber,at least two of the side walls are optically transmissive and, angularlyoffset from each other, and the device further comprises an opticssystem having at least one light source for transmitting light to thereaction chamber through a first one of the optically transmissive sidewalls and having at least one detector for detecting light emitted fromthe chamber through a second one of the optically transmissive sidewalls.
 16. The device of claim 12, wherein the body further includes avent in fluid communication with the second channel for venting gas fromthe second channel.
 17. The device of claim 12, further comprising adifferential pressure source for forcing fluid in the first channel inthe body to flow through the inlet port of the vessel and into thereaction chamber.
 18. The device of claim 12, wherein the vesselincludes: i) a rigid frame defining side walls of the reaction chanber;and ii) first and second polymeric films attached to opposite sides ofthe rigid frame to form opposing major walls of the reaction chamber.19. The device of claim 18, wherein each of the major walls issufficiently flexible to conform to a respective thermal surface. 20.The device of claim 18, wherein at least two of the side walls areoptically transmissive and angularly offset from each other.
 21. Thedevice of claim 12, wherein the ratio of the width of the reactionchamber to the thickness of the reaction chamber is at least 4:1, andwherein the reaction chamber has a thickness less than 2 mm.
 22. Thedevice of claim 12, wherein the body further includes a mixing chamberfor mixing the analyte with amplification reagents, the mixing chamberbeing connected to the inlet port of the vessel via the first channel.23. A device for conducting a chemical reaction, the device comprising:a) a body having at least first and second channels formed therein; andb) a reaction vessel extending from the body, the reaction vesselhaving: i) a plurality of walls defining a reaction chamber, at leastone of the walls comprising a flexible sheet or film; ii) an inlet portconnected to the reaction chamber via an inlet channel; and iii) anoutlet port connected to the reaction chamber via an outlet channel,wherein the inlet port of the vessel is connected to the first channelin the body, and wherein the outlet port of the vessel is connected tothe second channel in the body; c) at least one thermal surface forcontacting the sheet or film; d) means for increasing the pressure inthe reaction chamber, wherein the pressure increase in the chamber issufficient to force the sheet or film to conform to the thermal surface;and e) at least one thermal element for heating or cooling the surfaceto induce a temperature change in the chamber.
 24. The device of claim23, wherein the walls defining the reaction chamber include two opposingmajor walls and sidewalls connecting the major walls to each other, atleast two of the side walls are optically transmissive, and the devicefurther comprises an optics system having at least one light source fortransmitting light to the reaction chamber through a first one of theoptically transmissive side walls and having at least one detector fordetecting light exiting the chamber through a second one of theoptically transmissive side walls.
 25. The device of claim 23, whereinthe body further includes a vent in fluid communication with the secondchannel for venting gas from the second channel.
 26. The device of claim23, further comprising a differential pressure source for forcing fluidin the first channel in the body to flow through the inlet port of thevessel and into the reaction chamber.
 27. The device of claim 23,wherein the walls defining the reaction chamber include two opposingmajor walls and sidewalls connecting the major walls to each other, andwherein the vessel includes: i) a rigid frame defining the side walls;and ii) first and second polymeric films attached to opposite sides ofthe rigid frame to form the opposing major walls.
 28. The device ofclaim 27, wherein at least two of the side walls are opticallytransmissive and angularly offset from each other.
 29. The device ofclaim 23, wherein the ratio of the width of the chamber to the thicknessof the chamber is at least 4:1, and wherein the chamber has a thicknessless than 2 mm.
 30. The device of claim 23, wherein the body furtherincludes a mixing chamber for mixing nucleic acid with amplificationreagents, the mixing chamber being connected to the inlet port of thevessel via the first channel.
 31. The device of claim 23, wherein thebody has formed therein: i) a sample flow path; and ii) a separationregion in the sample flow path for separating a desired analyte from afluid sample, the separation region being connected to the inlet port ofthe vessel via the first channel.
 32. The device of claim 31, whereinthe separation region in the body comprises: a) a lysing chamber in thesample flow path for lysing cells or viruses in the sample to releasematerial therefrom; and b) at least one solid support positioned in thelysing chamber for capturing the cells or viruses to be lysed.
 33. Adevice for conducting a chemical reaction, the device comprising: a) abody having at least first and second channels formed therein; and b) areaction vessel extending from the body, the reaction vessel having: i)a rigid frame defining side walls of a reaction chamber; ii) first andsecond polymeric films attached to opposite sides of the rigid frame toform opposing major walls of the reaction chamber; wherein at least twoof the walls of the reaction chamber are optically transmissive; iii) aninlet port connected to the reaction chamber via an inlet channel; andiv) an outlet port connected to the reaction chamber via an outletchannel, wherein the inlet port of the vessel is connected to the firstchannel in the body and wherein the outlet port of the vessel isconnected to the second channel in the body; and c) optics for opticallyinterrogating the reaction chamber, the optics comprising at least onelight source for transmitting light to the reaction chamber through afirst one of the optically transmissive walls and at least one detectorfor detecting light exiting the chamber through a second one of theoptically transmissive walls.
 34. The device of claim 33, wherein thebody further includes a vent in fluid communication with the secondchannel for venting gas from the second channel.
 35. The device of claim33, further comprising a differential pressure source for forcing fluidin the first channel in the body to flow through the inlet port of thevessel and into the reaction chamber.
 36. The device of claim 33,wherein the at least two optically transmissive walls comprise at leasttwo of the side walls, and wherein the at least two opticallytransmissive side walls are angularly offset from each other.
 37. Thedevice of claim 33, wherein the ratio of the width of the chamber to thethickness of the chamber is at least 4:1, and wherein the chamber has athickness less than 2 mm.
 38. The device of claim 33, wherein the bodyfurther includes a mixing chamber for mixing nucleic acid withamplification reagents, the mixing chamber being connected to the inletport of the vessel via the first channel.
 39. The device of claim 33,wherein the body further has formed therein: i) a sample flow path; andii) a separation region in the sample flow path for separating a desiredanalyte from a fluid sample, the separation region being connected tothe inlet port of the vessel via the first channel.
 40. The device ofclaim 33, wherein the separation region in the body comprises: a) alysing chamber in the sample flow path for lysing cells or viruses inthe sample to release material therefrom; and b) at least one solidsupport positioned in the lysing chamber for capturing the cells orviruses to be lysed.
 41. The device of claim 33, further comprising: a)at least one thermal surface for contacting at least one of the films;and b) at least one thermal element for heating or cooling the surfaceto induce a temperature change in the chamber.
 42. A device forconducting a chemical reaction, the device comprising: a) a body having:i) a sample flow path; and ii) a separation region in the sample flowpath for separating a desired analyte from a fluid sample; b) a reactionvessel extending from the body, the reaction vessel having: i) areaction chamber defined by two opposing major walls and side wallsconnecting the major walls to each other, at least two of the wallsdefining the reaction chamber being optically transmissive; ii) an inletport connected to the reaction chamber via an inlet channel; and iii) anoutlet port connected to the reaction chamber via an outlet channel,wherein the body further has at least first and second channels formedtherein, the separation region being connected to the inlet port of thevessel via the first channel in the body, and the outlet port of thevessel being connected to the second channel in the body; and c) opticsfor optically interrogating the reaction chamber, the optics comprisingat least one light source for transmitting light to the reaction chamberthrough a first one of the optically transmissive walls and at least onedetector for detecting light exiting the chamber through a second one ofthe optically transmissive walls.
 43. The device of claim 42, whereinthe body further includes a vent in fluid communication with the secondchannel for venting gas from the second channel.
 44. The device of claim42, further comprising a differential pressure source for forcing fluidin the first channel in the body to flow through the inlet port of thevessel and into the reaction chamber.
 45. The device of claim 42,wherein the vessel includes: i) a rigid frame defining the side walls;and ii) polymeric films attached to opposite sides of the rigid frame toform the two opposing major walls.
 46. The device of claim 42, whereinthe at least two optically transmissive walls comprise at least two ofthe side walls, and wherein the at least two optically transmissive sidewalls are angularly offset from each other.
 47. The device of claim 42,wherein the ratio of the width of the chamber to the thickness of thechamber is at least 4:1, and wherein the chamber has a thickness lessthan 2 mm.
 48. The device of claim 42, wherein the body further includesa mixing chamber for mixing nucleic acid with amplification reagents,the mixing chamber being connected to the inlet port of the vessel viathe first channel.
 49. The device of claim 42, wherein the separationregion in the body comprises: a) a lysing chamber in the sample flowpath for lysing cells or viruses in the sample to release materialtherefrom; and b) at least one solid support positioned in the lysingchamber for capturing the cells or viruses to be lysed.
 50. The deviceof claim 42, wherein at least one of the major walls comprises aflexible sheet or film, and the device further comprises: a) at leastone thermal surface for contacting the sheet or film; and c) at leastone thermal element for heating or cooling the surface to induce atemperature change in the chamber.